Microprocessor system for the analysis of physiologic and financial datasets

ABSTRACT

A system and method for organization and analysis of complex and dynamically interactive time series is disclosed. One example comprises a processor based system for relational analysis of physiologic signals for providing early recognition of catastrophic and pathologic events such as pathophysiologic divergence. The processor is programmed to identify pathophysiologic divergence of at least one of first and second physiologic parameters in relationship to the other and to output an indication of the divergence. An object-based method of iterative relational processing waveform fragments in the time domain is described wherein each more complex waveform object inherits the characteristics of the waveform objects from which it is derived. The first physiologic parameter can be the amplitude and frequency of the variation in chest wall impedance or nasal pressure and the second parameter can be a measure or indication of the arterial oxygen saturation.

FIELD OF THE INVENTION

This invention relates to an object based system for the organization,analysis, and recognition of complex timed processes and the analysisand integration of time series outputs of data sets and particularlyphysiologic data sets, and to the evaluation of the financial andphysiologic datasets and the determination of relationships betweenthem.

BACKGROUND

The analysis of time series data is widely used to characterize thebehavior of a system. The following four general categories ofapproaches are commonly applied to achieve characterization of such asystem and these provide a general background for the present invention.The approaches are illustrative both in their conceptualization,application, and limitations.

The first such approach represents a form of mathematical reductionismof the complexity through the application of a cascade of rules based onan anticipated relationship between the time series output and a givenset of system mechanisms. In this approach the operative mechanisms,data set characteristics, and intruding artifact are a priori defined tothe best extent possible. Then a set of rules is applied to characterizeand analyze the data set based on predicted relationships between thedata set and the systems being characterized. Such systems often includecascading branches of decision-based algorithms, the complexity of whichincrease greatly in the presence of multiple interactive mechanisms. Thereductionism approach is severely limited by the uncertainty andcomplexity, which rapidly emerges when a cascade of rules is applied toa highly interactive data set, when the signal to noise ratio is low,and/or when multiple data sets generated by complex and dynamicallyinteractive systems are evaluated. These methods become inordinatelymore cumbersome as the complexity and number of time series increases.In addition the subtlety of the interactive and dynamic relationshipsalong and between datasets and the variations associated with thetechnique or tools of data collection often makes the cascading rulesvery difficult to a priori define.

The failure of simplification the analysis through mathematicalreductionism to adequately characterize the complex systems generatingsuch data sets, led to the perception that this failure resulted fromspecific limitations of a particular data format (usually the timedomain format). In other words, the time series was perceived to containsufficient information to characterize the system but, it was thought,that the recognition of this information required reformatting into adifferent mathematical representation, which emphasized other hiddencomponents which were specific for certain important systemcharacteristics. This approach is exemplified by frequency processingmethods, which reformat the time series into frequency components, suchas its sine components or wavelets, with the hope that patterns ofspecific frequency relationships within the system will emerge to berecognized. While often uncovering considerable useful information, thisapproach is remains quite limited when applied to highly complex andinteractive systems, because many complex relationships are poorlycharacterized by their frequency components, and it is often difficultto relate an output derived from frequency-based primitives to specificmechanisms operative within the system. In other words, the advantagesassociated with mathematically defined linkages between systemmechanisms and the rules based analysis provided by reductionism isreduced by the data reformatting process for the purpose of frequencybased signal processing as, for example, is provided by Fourier orwavelet transforms.

A third approach seeks to identify the patterns or relationships byrepetitively reprocessing the time series with a set of generalcomparative rules or by statistical processing. As with the datareformatting approach, the utility of this method in isolation (asembodied in neural network based analysis), is severely limited bydissociation of the output from the complex and interactive operativemechanisms, which define the output. With such processing, the relevantscope and characterization of the relationships of the output to theactual behavior of the dynamic interactions of the system is often quitelimited. This limits the applicability of such processing inenvironments wherein the characterization of behavior of the system as afunction by the output may be as important as the actual output valuesthemselves.

A fourth approach has been to apply chaotic processing to the timeseries. Again, like that of conventional signal processing thisalternative method is applied the expectation that some predictivepattern will emerge to be recognized. This technique shares several ofthe limitations noted for both frequency and statistical based datareformatting. In addition as, will be discussed, the application of thistype of processing to physiologic signals is limited by, redundant andinteractive higher control which greatly limits the progression of thesystem to a state of uncontrolled chaotic behavior. Such systems operatein environments of substantial interactive control until the developmentof a severe disease state, a point at which the diagnostic informationprovided by processing often has less adjective utility relevant timelyintervention.

The human physiologic system derives a large array of time seriesoutputs, which have substantial relevance when monitored over a finitetime interval. The human can be considered the prototypic complexinteractive system. These interactions and the mechanisms defining, themhave been the subject of intense research for over one hundred Nears andmost of this work has been performed the time domain. For this reasonany approach toward the characterization of such a system needs toconsider the value of engaging the body of knowledge, which relates tothese mechanisms. This has been one of the reasons that the reductionismhas predominated in the analysis of physiologic signals. U.S. Pat. Nos.5,765,563 to Vander Schaff, 5,803,066 to Rapoport, and 6,138,675 toBerthon-Jones show such simple cascade decision systems for processingphysiologic signals. U.S. Pat. No. 5,751,911 to Goldman shows areal-time waveform analysis system, which utilizes neural networks toperform various stages of the analysis. U.S. Pat. No. 6,144,877 toDepetrillo shows a processor based method for determining statisticalinformation for time series data and for detecting a biologicalcondition of a biological system from the statistical information. U.S.Pat. No. 5,782,240 and 5,730,144 to Katz shows a system, which applychaos analysers, which generate a time series, vector representation ofeach monitored function and apply chaotic processing to identify certainevents. All of these systems are deficient in that they are not able toadequately organize, order and analyze the true state of dynamicinteraction operative in the generation of these signals.

Critical illness is one example of a dynamic timed process, which ispoorly characterized by the above noted conventional methods. When humanphysiologic stability is under threat, it is maintained by a complexarray of interactive physiologic systems, which control the criticaltime dependent process of oxygen delivery to the organism. Each system(e.g. respiratory, cardiac or vascular) has multiple biochemical and/ormechanical controls, which operate together in a predictable manner tooptimize oxygen delivery under conditions of threat. For example anincreased oxygen requirement during infection causes the patient toincrease oxygen delivery by lowering lung carbon dioxide throughhyperventilation and the fall in carbon dioxide then causes thehemoglobin molecule to increase its affinity for oxygen thereby furtherenhancing oxygen delivery. In addition to the basic control of a singlesystem, other systems interact with the originally affected system toproducing a predictable pattern of response. For example, in thepresence of infection, the cardiac system interacts with the respiratorysystem such that both the stroke volume and heart rate increase. Inaddition, the vascular system may respond with a reduction in arterialtone and an increase in venous tone, thereby both reducing impedance tothe flow of oxygen to the tissues and shifting more blood into thearterial compartment.

Each system generally also has a plurality of predicable compensationresponses to adjust for pathologic alteration or injury to the systemand these responses interact between systems. For example thedevelopment of infectious injury to the lung will result in an increasein volume of ventilated gas to compensate for the loss of functionalsurface area. This increase in ventilation can then induce a synergisticincrease in both stroke volume and heart rate.

Finally a pathologic process altering one system will generally alsoinduce an alteration in one or more other systems and these processesare all time dependent. Sub acute or acute life threatening conditionssuch as sepsis, pulmonary embolism, or hemorrhage generally affect thesystems in cascades or predictable sequences which may have a timecourse range from as little as 20 seconds or more than 72 hours. Forexample, the brief development of airway collapse induces a fall inoxygen saturation, which then causes a compensatory hyperventilationresponse, which causes a rise in heart rate over as little as 20-30seconds. An infection, on the other hand, has a more prolonged timecourse inducing a rise in respiration rate, a rise in heart rate, andthen a progressive fall in oxygen saturation and finally a fall inrespiration rate and a finally a terminal fall in heart rate often overa course of 48-72 hours.

It can be seen therefore that each disease process engaging the organismcauses the induction of a complex and interactive time series ofpathophysiologic perturbation and compensation. At the onset of thedisease (such as early in the course of infection) the degree ofphysiologic change may be very slight and limited to one or twovariables. As a disease progresses both the magnitude of perturbationand the number of system involved increases. In addition to inducing apredictable range of perturbation, a particular disease processgenerally produces a specific range of progression and pattern ofevolution as a function of injury, compensation, and system interaction.Furthermore, this multi-system complexity, which can be induced byinitial pathologic involvement of a single system, is greatly magnified.When a plurality of pathologic processes is present.

Despite the tact that these conditions represent some of the mostimportant adversities affecting human beings, these pathologic processesare poorly characterized by even the most sophisticated of conventionalmonitors, which greatly oversimplify the processing and outputs. Perhapsthis is due to the fact that this interactive complexity overwhelmed thedevelopers of substantially all of the conventional physiologicsignal-processing methods in the same way that it overwhelms thephysicians and nurses at the bedside everyday. Hospital critical carepatient monitors have generally been applied as warning devices uponthreshold breach of specific critical parameters with the focus on thebalance between timely warning of a potentially life threateningthreshold breach and the mitigation of false alarms. However, during thepivotal time, early in the process of the evolution of critical illness,the compensatory responses limit the change in primary criticalvariables so that the user, monitoring these parameters in isolation, isoften given a false sense of security. For this reason it cannot beenough to recognize and warn of the occurrence of a respiratory arrest,or hypotension, or hypoxia, or of a particular type of cardiacarrhythmia. To truly engage and characterize the processes present, apatient monitor must have capability to properly analyze, organize, andoutput in a quickly and easily understood format the true interactivestate of critical illness. As discussed below, it is one of the purposesof the present invention to provide such a monitor

SUMMARY OF THE INVENTION

The present invention comprises a system and method, which providescomprehensive organization and analysis of interactive complexity alongand between pluralities of time series. One preferred embodiment of thepresent invention comprises an objects based method of iterativerelational processing of time series fragments or their derivativesalong and between corresponding time series. The system then applies aniterative comparison process of those fragments along and between aplurality time series. In this way, the relationship of a wide range ofcharacteristics of substantially any dynamic occurrence in one timeseries can be compare to the same or other characteristics ofsubstantially any dynamic occurrence along another portion of the sametime series or any of the processed corresponding time series.

According to the present invention, a first time series is processed torender a time series first level derived from sequential time seriessegments the first series, the time series first level is stored in arelational database, object database or object-relational database. Thefirst time series level is processed to render a second time serieslevel derived from the sequential time series component of the firsttime series level and these are stored in the relational database,object database or object-relational database. Additional levels arethen derived as desired. The compositions of sequential time series,which make up the first and second levels, are determined by thedefinitions selected for the respective segments from which each levelis derived. Each time series fragment is represented as a time seriesobject, and each more complex time series object inherits the more basiccharacteristics of time series objects from which they are derived.

The time course of sub acute and acute critical illness to point ofdeath is highly variable and can range from 24-72 hours with toxicshock, to as little as 30 seconds with neonatal apnea. The presentinventors recognized that, regardless of its time course, such apathological occurrence will have a particular “conformation”, whichaccording to the present invention can be represented spatially by anobject based processing system and method as a particular object or timeseries of objects, as a function of the specific progression of theinteractive components for the purpose of both processing and animation.The present inventors also recognized that the development of such aprocessing system would be capable of organizing and analyzing theinordinate degree of dynamic complexity associated with the output fromthe biologic systems through the automatic incorporation of these timeseries outputs into a highly organized relational, layered, object baseddata structure. Finally the inventors further recognized that because ofthe potentially rapid time course of these illnesses and theirreversible endpoint, that patient care monitors must provide a quicklyand easily understood output, which gives the medical personnel asimplified and succinct analysis of these complex relationships whichaccurately reflects the interactive complexity faced by the patient'sphysiologic systems.

It has been suggested that the development of periodicity in a humanphysiologic system represents a simplification of that system. Thisconcept is based on the perception that the human interactivephysiologic systems operates in an environment of chaos and that apartial loss of control, simplifies the relationships, allowing simplerperiodic relationships to emerge. However, there is considerable reasonto believe that this is not the case. Patients centering an environmentof lower partial pressure of oxygen, as at altitude, will developperiodicity of ventilation. This does not indicate a generalsimplification of the system but rather, one proposed operativemechanism for the emergence of this new pattern is that the patternreflects the uncovering of a preexisting dynamic relationship betweentwo controllers, which now, together determine ventilation in this newenvironment. At sea level the controller responding to oxygen wassubordinate the controller responding to carbon dioxide so that theperiodicity was absent. This simple illustration serves to demonstratethe critical linkage between patient outputs and higher control and thecriticality of comprehensively comparing dynamic relationships along andbetween signals to achieve a true picture of the operative physiology.While periodicities are, at times, clearly pathologic, their developmentin biologic systems, rather than a manifestation of simplification ofphysiological behavior, than the engagement of new, often represents theengagement of more rudimentary layers of protection of a particularorgan function or range built into the control system. This illustrationfurther demonstrates that a given physiologic signal, when monitored inisolation, may appear to exhibit totally unpredictable and chaoticbehavior, but when considered in mathematical or graphical relation (asin phase space) to a plurality of corresponding interactive signals, andto the interactive control mechanisms of those corresponding signals,the behavior of the original, chaotic appearing, signal often becomesmuch more explicable.

In an example, consider a timed plot of oxygen saturation (SPO2) underheavy sedation during sleep. This state is often associated with a lossof the maintenance of a narrow control range of ventilation during sleepand with the loss of stability of the airway so that a plot of theoxygen saturation, in the presence of such deep sedation, shows a highlyvariable pattern, which often appears grossly unpredictable, withsustained falls in oxygen saturation intermixed with rapid falls andoften seemingly random rapid corrections. However, there are definablelimits or ranges of the signal, and generally definable patterns, whichare definable within the background of a now highly variable SPO2signal. It may be temping to define this behavior statistically or by achaotic processor in the hope of defining some emerging patterns as afunction of the mathematical behavior of that signal. However, whenanalyzed with the partial pressure of CO2, the minute ventilation, and aplot of EEG activity the oxygen saturation values are seen as asubordinate signal to the airflow which is now being controlled by adysfunctional control process, which process is being salvaged by a morecoarse and rudimentary survival response mechanism. The apparentlychaotic behavior is now seen as driven by a complex but predictablesequence of a plurality of dynamic interactive relationships betweencorresponding signals and the forces impacting them. Therefore, in thepresence of a pathophysiologic process, the behavior and ranges of anygiven signal are optimally defined by the dynamic patterns of theinteractive behavior of corresponding signals and their respectivedynamic ranges.

A biologic system actually exploits the chaotic output of simplenonlinear relationships by defining control ranges, which are affectedby variations in corresponding signals. This produces a great degree indiversity of dynamic physiologic response, which is beneficial in thatit may favor survival of a particular subgroup, in the presence of acertain type of pathophysiologic threat. The present inventors notedthat, while this diversity imparts greater complexity, this complexitycan be ordered by the application iterative microprocessor system, whichdefines a given signal as a function of a range “dynamic normality”.According to one embodiment of the present invention, each signal isdefined as a function of its own dynamic range (and in relation to apredicted control range) and as a function of contemporaneously relevantrelationships of the dynamic ranges of other corresponding signals (withrespect to their respective control ranges).

In a preferred embodiment the present invention comprises a system andmethod for organizing and anal zing multiple time series of parametersgenerated by a patient (as during critical illness) and outputting thisanalysis in readily understandable format. The preferred system iscapable of simultaneously processing dynamic time series of physiologicrelationships in real time at multiple levels along each parameter andacross multiple levels of different parameters. The present inventionprovides this level of interactive analysis specifically to match thecomplexity occurring during a pathologic occurrence. More specificallythe present invention provides an analysis system and method, whichanalyses the true dynamic state of a biologic system and the interactiveprimary and compensatory perturbations defining that state. Duringhealth the output of physiologic systems are maintained within tightvariances. As will be discussed, using the signal processing system ofthe present invention the extent to which the signals are held withinthese tight variances are characterized as a function of their dynamicranges of variance and the signals are further characterized as afunction their dynamic relationships along the time series within agiven signal and between a plurality of additional correspondingsignals. As will be learned by the following disclosure, the optimalmonitor of the human physiologic state during critical illness must becapable of analyzing time series relationships along and between aplurality signals with the similar degree of analytic complexity as isoperative in the biologic systems controlling the interactive responseswhich are inducing those signals and of outputting an indication basedon the analysis in a readily understandable format. In the preferredembodiment this is provided as a dynamic format such as atwo-dimensional or three-dimensional object animation, the configurationof which is related to the analysis output. The configurations of theanimation changes with the analysis output, as this output changes overtime in relation to changes in the patient's physiologic state. Theanimation thereby provides a succinct and dynamic summary renderingwhich organizes the complexity of the interactive components of theoutput so that they can be more readily understood and used at thebedside and for the purpose of patient management and education ofmedical staff relevant the application of time series analysis in theassessment of disease. According to a preferred embodiment of thepresent invention the process proceeds by the following sequence;

-   -   Organize the multiple data streams defining the input into a        hierarchy of time series objects in an objects based data        structure.    -   Analyze and compare of the objects along and across time series,    -   Organize and summarize (and/or simplify) the output.    -   Animate and present the summarized output.    -   Take action based on the output.    -   Analyze and compare the new objects derived subsequent the        action.    -   Adjust the action.    -   Repeated the cycle    -   Calculate the expense and recourse utilization related to said        output

Using the above system, according to the present invention, a pluralityof time series of physiologic signals (including timed laboratory data)of a given physiologic process (such as sepsis) can have a particularconformational representation in three-dimensional space (as is shown inFIGS. 2 a and 2 b). This spatial representation comprises a summary ofthe relational data components, as analyzed, to diagnose a specificpathophysiologic process, to determine its progression, to define itsseverity, to monitor the response to treatment, and to simplify therepresentative output for the health care worker.

Two exemplary pathophysiologic processes (airway instability and sepsis)will be discussed below and exemplary patient monitoring systems andmethods according to the present invention, for processing, organizing,analyzing, rendering and animating output, and taking action (includingadditional testing or treatment based on said determining) will bedisclosed.

A major factor in the development of respiratory failure is airwayinstability, which results in air-way collapse during sedation, stroke,narcotics, or stupor. As illustrated in FIGS. 5 a and 5 b, such collapseoccurs in dynamic cycles called apnea clusters affecting a range ofphysiologic signals. These apnea clusters are an example of a common andpotentially life threatening process, which, perhaps due to the dynamicinteractive complexity of the time series, is not recognized byconventional hospital processors. Yet subgroups of patients in thehospital are at considerable risk from this disorder. Patients withotherwise relatively, stable airways may have instability induced bysedation or narcotics and it is critical that this instability berecognized in real time in the hospital so that the dose can be adjustedor the drug withheld upon the recognition of this development.Conventional patient monitors are neither configured to provideinterpretive recognition the cluster patterns indicative of airway andventilation instability nor to provide interpretative recognition of therelationship between apnea clusters. In fact, such monitors often applyaveraging algorithms, which attenuate the clusters. For these reasonsthousands of patients each day enter and leave hospital-monitored unitswith unrecognized ventilation and airway instability.

This failure of conventional hospital based central patient monitorssuch as Agilent CMS, or the GE-Marquette Solar 8000, to automaticallydetect, and quantify obstructive sleep apnea or the cluster patternsindicative of airway instability can be seen as a major health caredeficiency associated with a failure to address a long and unsatisfiedneed. Because sleep apnea is so common, the consequence of the failureof conventional hospital monitors to routinely recognize apnea clustersmeans that the diagnosis was missed in perhaps hundreds of thousands ofpatients who unknowingly have this disorder and who have been monitoredin the hospital over the past decade. Many of these patients will neverbe diagnosed in their lifetime and will needlessly suffer with thecomplications of the disorder. For these patients, the diagnosticopportunity was missed and the health implications and risk ofcomplications associated with undiagnosed airway instability and sleepapnea will persist in this group throughout the rest of their lifesimply because it was not recognized that simple modifications andprogramming of these devices could allow automatic recognition of thiscommon disorder. A second group of patients will have a complication inthe hospital due to the failure to timely recognize obstructive sleep orairway instability. Also an important opportunity to enhance the valueof a conventional critical care monitor, to increase the efficiency ofthe diagnosis of obstructive sleep apnea, and to increase the revenuefor the critical care monitoring companies marketing has been lost.Further an opportunity to increase hospital and/or physician revenue hasbeen missed, it is critical that obstructive sleep apnea and theclusters indicative of airway instability be automatically and routinelyrecognized by conventional hospital to reduce the needless occurrencesof respiratory failure, arrest, and/or death related to theadministration of IV sedation and narcotics to patients in the hospitalwith unrecognized airway instability.

To understand the criticality of recognizing airway instability inreal-time it is important to consider the significance of the combinedeffect that oxygen therapy and narcotics or sedation may have in thepatient care environment in the hospital, for example, in the managementof a post-operative obese patient after upper abdominal surgery. Such apatient may be at particular risk for increased airway instability inassociation with narcotic therapy in the 1^(st) and 2^(nd)post-operative day due to sleep deprivation, airway edema, and sedation.Indeed, many of these patients have significant sleep apnea prior toadmission to the hospital which is unknown to the surgeon or theanesthesiologist due to the subtly of symptoms. These patients, evenwith severe sleep apnea, are relatively safe at home because of anarousal response; however, in the hospital narcotics and sedatives oftenremove this “safety net”. The administration of post-operative narcoticscan significantly increase airway instability and, therefore, place thepatient at substantial risk. Many of these patients are placed onelectrocardiographic monitoring but the alarms are generally set at highand low limits. Hypoxemia, induced by airway instability generally doesnot produce marked levels of tachycardia; therefore, airway instabilityis poorly identified by simple electrocardiographic monitoring withoutthe identification of specific clusters of the pulse rate. In addition,simple oximetry evaluation is also a poor method to identify airwayinstability. Conventional hospital oximeters often have averagingintervals, which attenuate the dynamic desaturations. Even when theclustered desaturations occur they are often thought to represent falsealarms because they are brief when desaturations are recognized aspotentially real this often results in the simple and often misguidedaddition of nasal oxygen. However, nasal oxygen may prolong the apneasand potentially increase functional airway instability. From amonitoring perspective, the addition of oxygen therapy can be seen topotentially hide the presence of significant airway instability byattenuation of the level of desaturation and reduction in theeffectiveness of the oximeter as a monitoring tool in the diagnosis ofthis disorder.

Oxygen and sedatives can be seen as a deadly combination in patientswith severely unstable airways since the sedatives increase the apneasand the oxygen hides them from the oximeter. For all these reasons, aswill be shown, according to the present invention, it is critical tomonitor for the specific cluster patterns, which are present during theadministration of narcotics, or sedatives in patients with increasedrisk of airway instability.

The central drive to breath, which is suppressed by sedatives ornarcotics, basically controls two critical muscle groups. The upperairway “dilator muscles” and the diaphragm “pump muscles”. The tone ofboth these muscle groups must be coordinated. A fall in tone from thebrain controller to the airway dilators results in upper airwaycollapse. Alternatively, a fall in tone to the pump muscles causeshypoventilation.

Two major factors which contribute to respiratory arrest in the presenceof narcotic administration and sedation. The first and mosttraditionally considered potential effect of narcotics or sedation isthe suppression of the drive to pump muscles. In this situation airwayinstability may be less important than the reduced stimulation of thepump muscles, such as the diaphragm and chest wall, resulting ininadequate tidal volume and associated fall in minute ventilation and aprogressive rise in carbon dioxide levels. The rise in carbon dioxidelevels causes further suppression of the arousal response, therefore,potentially causing respiratory arrest. This first cause of respiratoryarrest associated with sedation or narcotics has been the primary focusof previous efforts to monitor patients postoperatively for the purposeof minimization of respiratory arrests. Both oximetry and tidal CO2monitoring have been used to attempt to identify and prevent thisdevelopment. However, in the presence of oxygen administration, oximetryis a poor indicator of ventilation. In addition, patients may have acombined cause of ventilation failure induce by the presence of bothupper airway instability and decreased diaphragm output. In particular,the rise in CO2 may increase instability of the respiratory controlsystem in the brain and, therefore potentially increase the potentialfor upper airway instability.

The second factor causing respiratory arrest due to narcotics orsedatives relates to depression of drive to upper airway dilator musclescausing a reduction in upper airway tone. This reduction in airway toneresults in dynamic airway instability and precipitates cluster cycles ofairway collapse and recovery associated with the arousal response as thepatient engages in a recurrent and cyclic process of arousal basedrescue from each airway collapse. If, despite the development ofsignificant cluster of airway collapse, the narcotic administration orsedation is continued, this can lead to further prolongation of theapneas and eventual respiratory arrest. There is, therefore, a dynamicinteraction between suppression of respiratory drive, which results inhypoventilation and suppression of respiratory drive, which results inupper airway instability. At any given time, a patient may have agreater degree of upper airway instability or a greater degree ofhypoventilation. The relative combination of these two events willdetermine the output of the monitor, with a former producing a simpletrending rise (as with end tidal CO2) or fall (as with minuteventilation or oxygen saturation) and the latter producing a clusteroutput pattern.

Unfortunately, this has been one of the major limitations of carbondioxide monitoring. The patients with significant upper airwayobstruction are also the same patients who develop significanthypoventilation. The upper airway obstruction may result in drop out ofthe nasal carbon dioxide signal due to both the upper airwayobstruction, on one hand, or be due to conversion from nasal to oralbreathing during a recovery from the upper airway obstruction, on theother hand. Although breath by breath monitoring may show evidence ofapnea, conversion from nasal to oral breathing can reduce the ability ofthe CO2 monitor to identity even severe hypoventilation in associationwith upper airway obstruction, especially if the signal is averaged orsampled at a low rate. For this reason, conventional tidal CO2monitoring when applied with conventional monitors may be leasteffective when applied to patients at greatest risk, that is, thosepatients with combined upper airway instability and hypoventilation.

As described in U.S. Pat. No. 6,223,064 (assigned to the presentinventor), the underlying cyclic physiologic process, which drives theperpetuation of a cluster of airway closures, can be exploited torecognize upper airway instability in real time. The underlying cyclicprocess, which defines the behavior of the unstable upper airway, isassociated Keith precipitous chances in ventilation and attendantprecipitous changes in monitored parameters, which reflect and/or areinduced by such ventilation changes. For example, cycling episodes ofairhead collapse and recovery produces sequential precipitous changes inwaveform output defining analogous cluster waveforms in the oximetrypulse tracing, the airflow amplitude tracing, the oximetry SpO₂ tracing,the chest wall impedance tracing and the EKG pulse rate or R to Rinterval tracing.

The use of central hospital monitors generally connected to plurality(often 5 or more) of patients through telemetry is a standard practicein hospitals. While the identification of sleep apnea in the hospital isrelatively common, at the present time, this requires the application ofadditional monitors. The present inventors are not aware of any of thecentral patient monitors (such as those in wide use which utilizecentral telemetry), which provide the above functionality. This isinefficient, requires additional patient connections, is not automatic,and is often unavailable. According to another aspect of the presentinvention, the afore referenced conventional hospital monitors areconverted and programmed to provide a measurement and count of airflowattenuation and/or oxygen desaturation and to compare that output withthe chest wall impedance to routinely identify the presence ofobstructive sleep apnea and to produce an overnight summary andformatted output for over reading for the physician which meets thestandard of the billing code in that it includes airflow, oximetry,chest impedance, and EKG or body position. This can use conventionalapnea recognition algorithms (as are well known in the art), the apnearecognition system of U.S. Pat. No. 6,223,064, or another system forrecognizing sleep apnea.

The prior art does not teach or anticipate the conversion of thesecentral hospital monitors to provide these functionalities despite themajor advantage for national heath care, which can be immediatelygained. However, the present inventors discovered and recognized thatthe addition of such functionality to central hospital monitors wouldquickly result in a profound advantage in efficiency, patient care,reduced cost, patient safety, and potentially enhances physician andhospital revenue thereby improving the method of doing the business ofdiagnosing and treating sleep apnea. The business of diagnosis of sleepapnea has long required additional equipment and would be greatlyenhanced by the conversion and programming of central hospital monitorsto provide this functionality. Moreover, the method of using theprocessor of a central hospital monitor to automatically detectobstructive sleep apnea and provide processor based interpretiveindication of obstructive output and to output a summary suitable forinterpretation to make a diagnosis of obstructive sleep apnea can resultin the automatic diagnosis of sleep apnea for hundreds of thousands ofpatients who are presently completely unaware of the presence of thisdisorder, and greatly improves the conventional method of doing thebusiness of diagnosing sleep apnea. This also allows the patientmonitoring companies, which manufacture the central hospital monitors toenter the sleep apnea diagnostic market and to exploit that entry byproviding telemetry connection of positive pressure devices to theprimary processor or secondary processor of the carried telemetry unitso that positive pressure can be adjusted by the patient monitor. Thisis an important method of doing the business of treating sleep apneasince it provides the hospital monitoring company with the potential forproprietary connectivity between the patient monitors and/or theassociated telemetry unit to the positive pressure devices therebyproviding a favorable mechanism for doing the business of sellingpositive pressure devices through enhancement of market entry and theincrease in the number of recognized cases.

According one aspect of the present invention, the recognition ofsequential precipitous changes can be achieved by analyzing the spatialand/or temporal relationships between at least a portion of a waveforminduced by at least a first apnea and at least a portion of a waveforminduced by at least a second apnea. This can include the recognition ofa cluster, which can compromise a high count of apneas with specifiedidentifying features which occur within a short time interval along saidwaveform (such as 3 or more apneas within about 5-10 minutes) and/or caninclude the identification of a waveform pattern defined by closelyspaced apnea waveform or waveform clusters. Further, the recognition caninclude the identification of a spatial and/or temporal relationshipdefined by waveform clusters, which are generated by closely spacedsequential apneas due to cycling upper airway collapse and recovery.Using the above discoveries typical standard hospital monitors can beimproved to provide automatic recognition of apnea clusters indicativeof upper airway instability and to provide an automatic visual oraudible indication of the presence of such clusters and further toprovide a visual or audible output and severity of this disorder therebyrendering the timely recognition and diagnosis of upper airwayinstability and obstructive sleep apnea as routine and automatic in thehospital as the diagnosis of other common diseases such as hypertension.

FIG. 5 a illustrates the reentry process driving the propagation ofapnea clusters. The physiologic basis for these clusters has beenpreviously described in U.S. Pat. Nos. 5,891,023 and 6,223,064 (thedisclosure of each of which is incorporated by reference as ifcompletely disclosed herein). This cycle is present when the airway isunstable but the patient is capable of arousal. In this situation, inthe sleeping or sedated patient, upon collapse of the airway, thepatient does not simply die she rescues herself and precipitously opensthe airway to recover by hypoventilation, however, if the airwayinstability remains after the arousal and rescue is over, the airwaycollapses again, only to be rescued again thereby producing a cluster ofclosely spaced apneas with distinct spatial, frequency and temporalwaveform relationships between and within apneas wherein the physiologicprocess reenters again and again to produce a clustered output.According to the present invention, an apnea cluster is comprised of aplurality (two or more) of closely spaced apneas or hypopneas but theuse of 3 or more apneas is preferred. The present invention includesrecognition of apnea clusters in SpO₂, pulse, chest wall impedance,blood pressure, airflow (including but not limited to exhaled carbondioxide and air temperature), systolic time intervals, andelectrocardiograph tracings including pulse rate and R to R intervalplots and timed plots of ST segment position and chest wall and/orabdominal movements. For all of these waveforms the basic underlyingcluster pattern is similar and the same basic presently preferred corecluster pattern recognition system and method, according to the presentinvention, can be applied to recognize them.

The present invention further includes a system for defining thephysiologic status of a patient during critical illness based on thecomparison of a first parameter along a first monitored time intervaldefining a first timed data set to at least one other parameter along asecond time interval, defining a second timed data set. The second timeinterval corresponds to the first time interval and can actually be thefirst time interval or another time interval. The second time intervalcorresponds to the effected physiologic output of the second parameteras inclined by the output of the first parameter during the first timeinterval. For example the first time interval can be a five to fifteenminute segment of timed airflow and the time interval can be a slightlydelayed five to fifteen minute segment of timed oxygen saturationderived from the airflow which defined the dataset of the first timeinterval.

According another aspect of the present invention, the microprocessoridentifies changes in the second parameter that are unexpected inrelationship to the changes in the first parameter. For example, whenthe microprocessor identifies a pattern indicative of a progressive risein minute ventilation associated with a progressive fall in oxygensaturation, a textual warning can be provided indicating physiologicdivergence of the oxygen saturation and minute ventilation. For example,the term “divergent oxygen saturation” can be provided on the patientmonitor indicating that an unexpected change in oxygen saturation hasoccurred in association with the ventilation output. The occurrence ofsuch divergence is not necessarily a life threatening condition but canbe an early warning of significant life threatening conditions such aspulmonary embolism or sepsis. If the patient has an attached apparatuswhich allows the actual minute ventilation to be quantitatively measuredrather than trended then, divergence can be identified even when theoxygen saturation does not fall as defined by plotting the timed outputof ventilation indexing oximetry as by formulas discussed in the U.S.patent applications (of one of the present inventors) entitled MedicalMicroprocessor System and Method for providing, a Ventilation IndexedValue 60/201,735 and Microprocessor system for the simplified diagnosisof sleep apnea Ser. No. 09/115,226 (the disclosure of each of which isincorporated herein b reference as if completely disclosed herein). Uponthe identification of divergence, the time series of other parameterssuch as the temperature, while blood cell count and other lab tests canbe included to identify the most likely process causing, the divergence.

One of the reasons that the identification of pathophysiologicdivergence is important is that such identification provides earlierwarning of disease. In addition, if the patient progresses to developsignificantly low levels of a given parameter, such as oxygen saturationor pulse, it is useful to be able to go back and identify whether or notthe patient experienced divergence of these parameters earlier sincethis can help identify whether it is a primary cardiac or pulmonaryprocess which is evolving and indeed the time course of the physiologicprocess is provided by both diagnostic and therapeutic. Consider, forexample, a patient experiencing significant drop in oxygen saturationand cardiac arrest. One purpose of the present invention is to providean output indicative of whether or not this patient experienced acardiac arrhythmia which precipitated the arrest or whether someantecedent pulmonary process occurred which caused the drop in oxygensaturation which then ultimately resulted in the cardiac arrhythmia andarrest. If the patient is being monitored by chest wall impedance,oximetry and EKG, all three parameters can be monitored for evidence ofpathophysiologic divergence. If, according to the present invention, theprocessor identifies divergence of the oxygen saturation in associationwith significant rise in minute ventilation, then consideration forbedside examination, chest x-ray, arterial blood gas measurement can allbe carried out so that the relationship between cardiac and pulmonarycompensation in this patient can be identified early rather than waitinguntil a threshold breach occurs in one single parameter. Since, with theuse of conventional monitors, threshold breach of an alarm can beseverely delayed prevented by an active compensatory mechanism, such ashyperventilation, one advantage of the present invention is that theprocessor can provide warning as much as 4 to 8 hours earlier byidentifying pathophysiologic divergence rather than waiting for thedevelopment of a threshold breach.

Another example of the value of monitor based automatic divergencerecognition, according to the present invention is provided by a patientwho has experienced a very mild breach of the alarm threshold inassociation with significant physiologic divergence such as a patientwhose baseline oxygen saturation is 95% in association with a givenbaseline amplitude and frequency of minute ventilation as identified bythe impedance monitor. For this patient, the fall in oxygen saturationover a period of two hours from 95% to 89% might be perceived by thenurse or house officer as representing only a mild change which warrantsthe addition of simple oxygen treatment by nasal cannula but no furtherinvestigation. However, if this same change is associated with markedphysiologic divergence wherein the patient has experienced significantincrease in the amplitude and frequency of the chest impedance, themicroprocessor identification of significant pathophysiologic divergencecan give the nurse or house officer cause to consider furtherperformance of a blood gas, chest x-ray or further investigation of thisotherwise modest fall in the oxygen saturation parameter.

It is noted that excessive sedation is unlikely to produce physiologicdivergence since sedation generally results in a fall in minuteventilation, which will be associated with a fall in oxygen saturationif the patient is not receiving nasal oxygen. The lack ofpathophysiologic divergence in association with a significant fall inoxygen saturation can provide diagnostic clues to the house officer.

In a preferred embodiment, the processor system can automatically outputan indication of pathophysiologic divergence relating to timed data setsderived from sensors which measure oxygen saturation, ventilation, heartrate, plethesmographic pulse, and/or blood pressure to provide automaticcomparisons of linked parameters in real time, as will be discussed. Theindication can be provided in a two or three-dimensional graphicalformat in which the corresponding parameters are presented summarygraphical format such as a timed two-dimensional or three-dimensionalanimation. This allows the nurse or physician to immediately recognizepathophysiologic divergence.

According to another aspect of the invention the comparison of signalscan be used to define a mathematical relationship range between twoparameters and the degree of variance from that range. This approach hassubstantial advantages over the simple comparison of a given signal%kith itself along a time series to determine variability with respectto that signal (as is described in Griffin U.S. Pat. No. 6,216,032, thedisclosure of which is incorporated by reference as is completelydisclosed herein), which has been shown to correlate loosely with adiseased or aged physiologic system. The signal variability processingmethod of the prior art, which has been widely used with pulse rate,lacks specificity since variance in a given signal may have many causes.According to the present invention a plurality of signals are tracked todetermine if the variability is present in all of the signals, to definethe relationship between the signals with respect to that variability,and to determine if a particular signal (such as for example airflow) isthe primary (first) signal to vary with other signals tracking theprimary signal. For example, airway instability, sepsis, stroke, andcongestive heart failure are all associated with a high degree of heartrate variability and this can be determined in relation to a baseline orby other known methods, however in the preferred embodiment the generalvariability of a plurality of signals is determined and these arematched to determine if a particular signal has a greater variabilitythan the other signals, and more importantly the dynamic relationshipbetween the signals is determined to identify the conformation of thatvariability. In this respect for example the pulse in sepsis in aneonate may show a high degree of variability, by confirming that thisvariability is associated with a general multi-parameter conformation asshown in FIGS. 2 a and 2 b(and will be discussed in more detail) ratherthan a conformation of rapidly expanding and contracting parameters, asis typical of airway instability. In this way the etiology of the pulsevariability is much better identified. Variability is therefore definedin relation to; which parameters are changing, whether they are changingtogether in a particular category of conformation indicative of aspecific disease process, and the extent to which they followanticipated subordinate behavior is identified. According to anotheraspect of the present invention the time series of the parameter“relationship variance” and the time series of the “relationshipvariability” are analyzed as part of the cylindrical data matrix.

Early in the state of sepsis airflow and heart rate variability begin todevelop. However early the oxygen saturation is closely linked to theairflow tracking the airflow and showing little variance near the top ofits range. As septic shock evolves variability increases and the tightrelationship between airflow and oxygen saturation begins to breakdown.In one preferred embodiment, this relationship is analyzed, as timeseries of the calculated variance of the airflow, variance of the heartrate, and variance of the oxygen saturation, along with the streamingtime series of objects of the original measured values. Timed calculatedvariability thereby comprising components of a cylindrical data matrixof objects analyzed according to the methods described herein for timeseries analysis. Furthermore a time series of the variance from a givenrelationship and the variability of that variance is derived and addedto the data matrix. In an example an index of the magnitude value ofairflow in relation to the magnitude value of oxygen saturationand/heart rate is calculated for each data point (after adjusting forthe delay) and a time series of this index is derived. Then a timeseries of the calculated variability of the index is derived and addedto the data matrix. The slope or trend of the index of “airflow” andoxygen saturation will rise significantly as septic shock evolves andthis can be correlated with the slope of the variability of the of thatindex. In comparison with septic shock in airway instability, timeseries of these parameters shows a high degree of variability generallybut a relatively low degree of variance of the indexed parametersassociated with that variability (since despite their precipitousdynamic behavior, these parameters generally move together maintainingthe basic relationships of physiologic subordinance). In addition toheart rate, a time series of the plethesmographic pulse (as amplitude,ascending slope, area under the curve, etc.) variability and variance(as with continous blood pressure or airflow) can be derived andincorporated with the data matrix for analysis and comparison todetermine variability and variance relationships as well as to definethe general collective conformation of the dynamic relationships of allof these parameters.

According to another aspect of the invention the analysis of subsequentportions of a time-series can automatically be adjusted based on theoutput of the analysis of preceding portions of a time-series. In anexample, with timed waveforms, such as SpO₂, in clinical medicine, thereare two situations: one in which motion is present wherein it iscritical to mitigate the effect of motion on the waveform and a secondsituation in which motion is not present, wherein it would be optimalnot to apply motion algorithms so that true accurate waveform can bereflected without smoothing. The application of motion algorithms on acontinuous basis results in significant smoothing of the entire waveformeven when motion is not present, thereby, attenuating the optimalfidelity of the waveform and potentially hiding important short termprecipitous changes. For example, the application of these algorithmsresults in modification of slope of the desaturation and the slope ofresaturation and affects the relative relationship between thedesaturation and resaturation slopes. One preferred embodiment of thepresent invention includes a conventional system and method fordetecting motion. The system and can include the motion detectionmethod, which are utilized by Masimo Incorporated or Nellcor PuritanBennett Incorporated and are well known in the art. According to thepresent invention, the signal is processed in one of two ways. If motionis detected the signal is processed through a motion mitigationalgorithm such as the Masimo SET, as is known in the art. Subsequently,this signal is processed with cluster analysis technology for therecognition of airway instability. The cluster analysis technology isadjusted to account for the effect of averaging on the slopes and thepotential for averaging to attenuate mild desaturations. In the secondinstance, when no motion is detected, the output is processed with ashorter averaging interval of about 1 to 2 seconds. This producesoptimal fidelity of the waveform. This waveform is then processed forevidence of airway instability using cluster recognition.

According to one aspect of the invention a microprocessor system isprovided for the recognition of specific dynamic patterns of interactionbetween a plurality of corresponding and related time series, the systemcomprising a processor the processor programmed to; process a first timeseries to produce a lower-level time series of sequential time seriesfragments derived from the first time series, process the lower-leveltime series to produce a higher-level time series comprised ofsequential time series fragments from the lower-level time series,process a second time series, the second time series being related tothe first time series, produce a second lower-level time series ofsequential time series fragments derived from the second time series,and identify a dynamic pattern of interaction between the first timeseries and the second time series. The system can be further programmedto process the lower-level time series of the second time series to;produce a higher-level time series derived from sequential time seriesfragments of the second lower-level time series. The system can beprogrammed to process a third time-series, the third time series beingrelated to at least one of the first and the second time series, toproduce a third lower-level time series of sequential time seriesfragments derived from said third time series. The system can beprogrammed to process the higher-level time series to produce acomplex-level time series derived from sequential time series fragmentsof said higher-level time series. The time series fragments of the firstand second time series can be stored in a relational database, thefragments of the higher-level time series can comprise objects, theobjects inheriting the characteristics of the objects of the lower-leveltime series from which they are derived. The first and second timeseries can comprise datasets of physiologic data points and the systemcan comprise a patient monitoring system wherein the dynamic pattern ofinteraction comprises pathophysiologic divergence.

In one presently preferred embodiment, the system comprises, a monitorhaving a plurality of sensors for positioning adjacent a patient and aprocessor programmed to; produce a first timed waveform based on a firstphysiologic parameter of the patient, produce a second timed waveformbased on a second physiologic parameter which is generally subordinateto the first physiologic parameter, so that the second parameternormally changes in response to changes in the first parameter, identifypathophysiologic divergence of at least one of the first and secondphysiologic parameters in relationship to the other physiologicparameter. The system can be further programmed to output an indicationof said divergence, calculate an index of said divergence and/or providean indication based on said index. The first parameter can, for example,comprise an indication of the magnitude of timed ventilation of apatient which can, for example, be the amplitude and/or frequency of thevariation in chest wall impedance and/or the amplitude and/or frequencyof the variation in nasal pressure and or the amplitude and frequency ofthe variation of at least one of the tidal carbon dioxide and/or thevolume of ventilation or other measurable indicator. The secondparameter can, for example, comprise a measure of oxygen saturation andcan be pulse oximetry value or other measurable indicator of arterialoxygenation such as a continous or intermittent measurement of partialpressure of oxygen.

Another aspect of the invention further includes a method of monitoringa patient comprising: monitoring a patient to produce a first timedwaveform of a first physiologic parameter and a second timed waveform ofa second physiologic parameter, the second physiologic parameter beingphysiologically subordinate to the first physiologic parameter,identifying a pattern indicative of divergence of at least one of saidwaveforms in relation to a physiologically expected pattern of the oneof the other of said waveforms and outputting an indication of saiddivergence. The first timed waveform can be, for example defined by atime interval of greater than about 5-20 minutes. The first and secondtime series can, for example, be physiologic time series derived fromairflow and pulse oximetry. The processor can comprise a primaryprocessor, and the system can include a secondary processor and at leastone of a diagnostic and treatment device, the primary processor beingconnectable to the secondary processor, the secondary processor beingprogrammed to control at least one of the diagnostic and treatmentdevice, the secondary processor being programmed to respond to theoutput of said primary processor. The primary processor can beprogrammed to adjust the said program of said secondary processor. Thetreatment device can be, for example an airflow delivery systemcontrolled by a secondary processor, the secondary processor beingprogrammed to recognize hypopneas, the primary processor adjusting theprogram of said secondary processor based on the identifying. In anotherembodiment the treatment device can be an automatic defibrillator. Thesecondary processor can be mounted with at least one of the treatmentand diagnostic device, the primary processor being detachable from theconnection with the secondary processor. In one embodiment the primaryprocessor is a hospital patient monitor capable of monitoring andanalyzing a plurality of different patient related signals, whichinclude electrocardiographic signals. In an embodiment the primaryprocessor is a polysomnography monitor capable of monitoring a pluralityof different signals including encephalographic signals.

It is the purpose of the present invention to provide a monitor capableof organizing the complexity of the actual operative dynamicinteractions of all of the signals both with respect to the absolutevalues, the degree of relative variation, and rate of variation acrossalong and across multiple levels of the processed output and, morespecifically, along and across multiple levels of multiple signals.

It is further the purpose of the present invention to organize theinteractive complexity defining the physiologic outputs generated by theaffected physiologic systems, to recognize specific types and ranges ofinteractive pathophysiologic time series occurrences, and to analyze thecomponents and evolution of such occurrences, thereby providing a timelyoutput which reflects the true interactive, multi-system processimpacting the patient or to take automatic action base on the result ofsaid analysis.

It is the purpose of the present invention to provide an iterativeprocessing system and method which analyzes both waveforms and timedlaboratory data and outputs the dynamic evolution of the interactivestates of perturbation and compensation of physiologic systems inreal-time to thereby provide a device which actually monitors andrecognizes the true physiologic state of the patient.

It is the purpose of the present invention to provide an iterativeobject oriented waveform processing system, which can characterize,organize, and compare multiple signal levels across a plurality ofsignals by dividing each waveform level of each signal into objects fordiscretionary comparison within a relational database, object databaseor object-relational database

It is the purpose of the present invention to provide a diagnosticsystem, which can convert conventional hospital-based central telemetryand hard wired monitoring systems to provide automatic processor basedrecognition of sleep apnea and airway instability and which can outputthe data sets in a summary format so that this can be over read by thephysician so that sleep apnea can be automatically and routinelydetected in a manner similar to that of other common diseases such ashypertension and diabetes.

It is the purpose of the present invention to provide a diagnosticsystem, which can convert conventional hospital-based central telemetryand hard wired monitoring systems to provide processor based recognitionof sleep apnea and airway instability though the recognition of patternsof closely spaced apneas and/or hypopneas both in real time and inovernight interpretive format.

It is the purpose of the present invention to provide a system, whichidentifies, maps, and links waveform clusters of apneas fromsimultaneously derived timed signals of multiple parameters includingchest wall impedance, pulse, airflow, exhaled carbon dioxide, systolictime intervals, oxygen saturation, EKG-ST segment level, and otherparameters to enhance the real-time and overnight diagnosis of sleepapnea.

It is further the purpose of the present invention to provide timely,real-time indication such as a warning or alarm of the presence of apneaand/or hypopnea clusters so that nurses can be aware of the presence ofa potentially dangerous instability of the upper airway during titrationof sedatives and/or narcotics.

It is further the purpose of the present invention to provide a systemfor the recognition of airway instability for combined cluster mappingof a timed dataset of nasal oral pressure with tidal CO2 to identifyclusters of conversion from nasal to oral breathing and to optimallyrecognize clusters indicative of airway instability in association withtidal CO2 measurement indicative of hypoventilation.

It is further the purpose of the present invention to identifypathophysiologic divergence of a plurality of physiologically linkedparameters along a timed waveform over an extended period of time toprovide earlier warning or to provide reinforcement of the significanceof a specific threshold breach.

Another purpose of the present invention to identify an anomalous trendof a first respiratory output in relation to a second respiratory outputwherein said first output is normally dependent on said second output toidentify divergence of said first respiratory output in relationship tothe expected trend said first respiratory output based on the trend ofsaid second output.

A further purpose of the present invention is to plot the prolongedslope of a first respiratory output in relationship to the prolongedslope of a second respiratory output and to identify divergence of saidfirst respiratory output in relation to the slope second respiratoryoutput.

It is further the purpose of the present invention to provide a system,which automatically triggers testing (and comparison of the output) of asecondary intermittently testing monitor based on the recognition of anadverse trend of the timed dataset output of at least one continuouslytested primary monitor.

Another purpose of the present invention is to provide recognition oflower airway obstruction (as with bronchospasm or chronic obstructivepulmonary disease) by exploiting the occurrence of the forced exhalationduring the hyperventilation phase of recovery intervals after and/orbetween intermittent upper airway obstruction to identify obstructiveflow patterns within the forced exhalation tracing and thereby identifylower airway obstruction superimposed on clustered upper airwayobstruction.

It is another aspect of the present invention to provide a system thatautomatically customizes treatment algorithms or diagnostic algorithmsbased on the analysis of waveforms of the monitored parameters.

A further aspect of the present invention is to provide a method ofdoing business through linking a time series of expense and/ billingdata to a time series of patient related outputs and exogenous actionsapplied to the patient so that the expense of each aspect of thepatients care can be correlated with both the procedures and medicationsadministered as well as the patient output both with respect to dynamicpatterns of interaction and specific laboratory values or comparativeresults.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 a show a shows a three-dimensional representation of thecylindrical data matrix comprised of corresponding, streaming, timeseries of objects from four different timed data sets, with each of thefour data sets divided into an ascending hierarchy of 3 levels.

FIG. 1 b shows a portion of FIG. 1 a curved back upon it illustrate theflexibility of object comparison between levels and different data setswithin the same time period and across different levels of differentdata sets at different time periods to identify a dynamic pattern ofinteraction between the data sets.

FIG. 2 a shows a three-dimensional representation of collectiveconformation of corresponding time series of objects of pulse (which canbe heart rate and/or pulse amplitude), oxygen saturation, airflow, chestwall movement, blood pressure, and inflammatory indicators during earlyinfection, organized according to the present invention.

FIG. 2 b shows the representation of the dynamic multi-parameterconformation of the FIG. 2 a extended through the evolution of septicshock to the death point (the point of pathologic divergence of theoxygen saturation and airflow is identified along this representation).

FIG. 3 a shows a time series of raw data points.

FIG. 3 b shows a time series of dipole objects.

FIG. 3 c shows a time series of a slope set of the dipole objects ofFIG. 3 b, which removes the spatial attributes of the points andhighlights relative change

FIG. 3 d shows a time series with critical boundary points from whichthe wave pattern can be segmented and the objects can be derived andassociated properties calculated.

FIG. 3 e shows a time series of trend parameters calculated to providethe trend (or polarity) analysis.

FIG. 3 f shows one wave pattern of FIG. 3 d, which can be derived fromthe utilization of user-defined object boundaries

FIG. 3 g shores a representation for the manipulation by the user forslope deviation specification

FIG. 3 h shows a representation (or the manipulation by the user forduration deviation specification

FIG. 4 shores the organization of the waveforms of FIGS. 3 a-3 h intoascending object levels according to the present invention.

FIG. 5 a shows an illustration of the complexity of the mechanismsdefining the timed interactions of physiologic systems induced by upperairway instability, which the present inventor calls an “apnea clusterreentry cycle”

FIG. 5 b shorts an illustration of a raw data set of a plurality ofsignals derived from the mechanism of FIG. 5 a and from which, accordingto the present invention be represented as multi-signalthree-dimensional hierarchal object as shown in FIG. 5 a.

FIG. 5 c shows a schematic representation of a portion of a multi-signalobject as derived from the multiple corresponding time series of FIG. 5b with three multi-signal recover objects up to the composite objectlevel identified for additional processing according to the presentinvention.

FIG. 6 a shows one preferred three-dimensional graphical output forclinical monitoring for enhanced representation of the dependent anddynamic relationships between patient variables, which the presentinventors term the “-monitoring cube”

FIG. 6 b shows a two-dimensional output of the “monitoring cube” duringa normal physiologic state.

FIG. 6 c shows a two dimensional output of the “monitoring cube” showingphysiologic convergence during an episode of volitionalhyperventilation.

FIG. 6 d shows a two dimensional output of the “monitoring cube” showingpathophysiologic divergence as with pulmonary embolism.

FIG. 6 e shows a two dimensional output of the “monitoring cube” showinga concomitant increase in blood pressure and heart rate. The cube wouldbe rotated to see which increase came first.

FIG. 7 shows a schematic of a processing system for outputting and/ortaking action based on the analysis of the time series processingaccording to the present invention.

FIG. 8 shows a schematic of a monitor and automatic patient treatmentsystem according to the present invention.

FIG. 9 shows corresponding data at the raw data level of airflow andoxygen saturation wherein the subordinate saturation signal segmentdemonstrates physiologic convergence with respect to the primary airflowsignal segment.

FIG. 10 shows the raw data level of FIG. 9 converted the composite levelwhere the data is now comprised of a time series of sequential compositeobjects derived from the data sets of airflow and oxygen saturationsignals.

FIG. 11 shows a selected composite subordinate object of oxygensaturation from FIG. 10 matched with its corresponding primary compositeobject of airflow, as they are stored as a function of dipole datasetsin the relational database, object database or object-relationaldatabase.

FIG. 12 shows a comparison between two data sets of airflow wherein atthe fundamental level the second data set shows evidence of expiratoryairflow delay during the recovery object, wherein the recovery object isrecognized at the composite level.

FIG. 13 shows a schematic object mapping at the composite level ofcorresponding signals of airflow and oxygen saturation according to thepresent invention.

FIG. 14 shores a schematic object mapping at the composite level of twosimultaneously measured parameters with a region of anticipatedcomposite objects according to the present intention.

FIG. 15 shows a schematic object mapping and scoring at the compositelevel of two simultaneously measured parameters with the region ofanticipated composite objects according to the present invention.

FIG. 16 shows a schematic of a system for automatically changing theprocessing analysis of subsequent time-series based on the analysisoutput of an earlier portion of the time series.

FIG. 17 shows a schematic of a system for customizing a CPAPauto-titration algorithm based on the analysis of multiple correspondingsignals.

FIG. 18 shows a schematic system for comparing multiple signals andacting on the output of the comparison according to the presentinvention.

DESCRIPTION OF THE PRESENTLY PREFERRED EMBODIMENTS:

The digital object processing system, according to the presentinvention, functions to provide multidimensional waveform objectrecognition both with respect to a single signal and multiple signals.Using this method, objects are identified and then compared and definedby, and with, objects from different levels and from different signals.FIG. 1 a provides a representation of one presently preferred relationaldata processing structure of multiple time series, according to thepresent invention. As this representation shows, a plurality of timeseries of objects are organized into different corresponding streams ofobjects, which can be conceptually represented as a cylindrical matrixof processed, analyzed, and objectified data 1 with time defining theaxis along the length of the cylinder 1. In this example the cylinder 1is comprised of the four time series streams of processed objects eachstream having three levels and all of the time series and theirrespective levels are matched and stored together in a relationaldatabase, object database or object-relational database. Each streamingtime series of objects as from a single signal or source (e.g. airflowor oximetry, as in a matrix of physiologic signals) is represented inthe main cylinder 1 by a smaller cylinder (2,3,4,5) and each of thesesmaller cylinders is comprised of a grouping of ascending levels of timeseries of streaming objects (6,7,8) with the higher levels being derivedfrom the level below it. The streaming objects in each ascending timeseries level are more complex with each new level, and these morecomplex objects contain the simpler objects of the lower levels as willbe described. FIG. 1 b shows a cut section 9 of the cylindrical datamatrix of FIG. 1 a curved back upon itself to illustrate the oneimportant advantage of organizing the data in this way in that eachobject from each grouping can be readily compared and matched to otherobjects along the grouping and can further be compared and matched toother objects from each other grouping. Furthermore, an object from onelevel of one signal at one time can be readily compared to an objectfrom another level of a different signal at a different time. The timeseries of streaming objects in FIG. 1 b are airflow, SPO2, pulse, and aseries of exogenous actions. This is a typical data structure, whichwould be used according to the present invention to monitor a patient atrisk for sudden infant death syndrome and this will be discussed belowin more detail.

Using this data structure highly complex patterns and subtlerelationships between interactive and interdependent streams of objectscan be readily defined by searching the matched object streams as willbe discussed. This allows for the recognition of the dynamic patterninteraction or conformation of the matrix of analyzed streaminginteractive objects. FIG. 2 a provides an illustration of oneconformation of a collection of analyzed time series during earlysepsis. This is progressed through septic shock to the death point inFIG. 2 b. Each particular expected conformation will be defined by thespecific parameters chosen and the manner in which they are analyzed. Inan extension of the example a time series of expenditures would reflecta significant increase in the slope of resource (as financial or otherrecourses), which begins at a recognition point. If no recognition pointoccurs (i.e. the patient dies without the condition being diagnosed) theresource object time series have a flat or even decreasing slope. Therecognition of a specific dynamic pattern of interaction occurrencefalling within a specified range is used to determine the presence andseverity of a specific of a biologic or physical process, and itscorrelation kith a time series of recourse allocation (such as timedexpenditures) and a time series of exogenous actions (such aspharmaceutical therapy or surgery) can be used to determine the cost andcauses of a given dynamic pattern of interaction and to better definethe efficacy of intervention. The conformation of FIGS. 2 a and 2 b canbe seen as comprising a progressive expansion, evolving to divergence ofthe parameters and eventual precipitous collapse and death. This can bereadily contrasted with the conformation of the cylindrical anal zeddata matrix derived from the same analysis of the same time seriesgrouping during the state of evolving airway instability associated withexcessive sequential or continuously infused dosing of sedation ornarcotics. In this case the pattern is one of precipitous, cyclic, andconvergent expansion and contraction with eventual terminal contractionand death.

The following discussion presents one preferred embodiment of thepresent invention for application to the patient care environment toachieve organization and analysis of physiologic data and particularlyphysiologic signals and timed data sets of laboratory data from patientsduring a specific time period such as a hospitalization or perioperativeperiod.

The interaction of physiologic signals and laboratory data isparticularly complex, and requires a widely varied analysis to achievecomprehensive recognition of the many dynamic patterns of interactionindicative of potential life threatening pathophysiologic events. Thiswide variation is due, in part, to the remarkable variation in bothpatient and disease related factors. Such analysis is best performed inreal-time to provide timely intervention. To accomplish this level oforganization and DPI identification through multiple levels of each dataset or waveform and then across multiple levels of multiple data sets orwaveforms, the system processes and orders all of the datasets from eachsystem of the patient into a cylindrical matrix with each of the smallercylinders containing the levels in a specific ascending fashion. Anillustrative example of one preferred method sequence for organizing thedata set of a single smaller cylinder (comprised of a single signal ofairflow) is shown in FIGS. 3 a-3 i.

According to this method, the processor first derives from a time seriesof raw data points (FIG. 3 a) a series of dipole objects with theirassociated polarities and slopes (FIG. 3 b). As shown in FIG. 3 c thesedipoles can be represented as a slope set which removes the spatialattributes of the points and highlights relative change. As shown inFIG. 3 c, various boundary types can be used to separate the dipolesinto composite sequential objects and the figure shows threeillustrative boundary types: pattern limits, inflection points, andpolarity changes. As shown in FIG. 3 d, the system now has the criticalboundary points from which the wave pattern can be segmented and thecomposite objects can be derived and associated properties calculated.Although this is represented here as linear segments, each compositeobject is actually comprised of the original set of dipoles so that theuser can choose to consider it a straight segment with one slope or acurved segment defined by the entire slope set of the segmented object.FIG. 3 e shows how the “trend” composite objects can be identified toprovide a simplified linear trend (or polarity) analysis.

Though the “trend” object set is very useful as shown in FIG. 3 e thetime series can be segmented into other composite objects derived fromthe utilization of more or different user-defined boundary types. Thiscan be useful even if the curved shapes can be analyzed in the simplertrend analysis because the selection of object boundaries at specificranges or deflections helps to organize the objects as a direct functionof changes in the physiologic output. In the example below all threeboundary types are employed to derive a wave pattern wire frame. Thewire frame provides a simplified and very manageable view of the patternand has boundary attributes that can be vary useful in waveform patternsearching. This type of object segmentation can be shown (FIG. 3 f) as aset of object slopes with associated durations with the spatialrelationships removed. As is shown in FIGS. 3 h and 3 i this provides arepresentation for the manipulation by the user for object slope orduration deviation specification. Such deviations may be specifiedspecifically to individual segment objects or may be globallydesignated. Deviations may or may not be designated symmetrically.Multiple deviations can be specified per segment with scoring attributes(weighted deviations) to provide even more flexibility to the user tosearch for and correlate derived patterns. These two figures below shotsspecified deviations per segment (but not weighted deviations) for slopeand duration.

In the above exemplary manner, the time series can be organized with itsassociated objects and user-specified deviations, all of which arestored and categorized in a relational database, object database orobject-relational database. Also as will be discussed, once processed,portions of such a time series can then be applied as target searchobjects to other waveforms to search for similar objects and to scoretheir similarity.

Illustrations 3 h-3 i illustrate the user selection of linear ranges ofvariations however, of course, according to the present invention, thoseskilled in the art will recognize that complex curved shape variationscan be specified in a similar way through the selection of specificranges in variations of the dipole slope data set (FIG. 3 c) definingthe ranges of the curved target search object. (It should be noted thatwhile the dipole set shown appears linearized, in fact, it can be seenthat the dipoles can contain all of the information in the data pointsso that any curve present in the original raw data can be reproduced.)It is cumbersome to input such ranges for each dipole so this can beprovided by specifying a curved shape and then moving a pointer adjacenta curved shape to identify a range of shapes defining a curved targetsearch object.

FIG. 4 illustrates the ascending object processing levels according tothe present invention, which are next applied to order the objects. Inthe preferred embodiment, these levels are defined for each signal andcomparisons can be made across different levels between differentsignals. The first level is comprised of the raw data set. The data fromthis first level are then converted by the processor into a sequence offundamental objects called dipoles to form the second (fundamentalobject) level. All of the objects, which will ultimately define complexmulti-signal objects, are comprised of these sequential fundamentalobjects having the simple characteristics of slope polarity, andduration. At this level, the dipoles can be processed to achieve a “bestfit” dipole matching of two or more signals (as will be discussed) andare used render the next level, called the “composite object level”.

The composite object level is comprised of sequential and overlappingcomposite objects, which are composed of a specific sequence of slopedipoles as defined by selected search criteria. Each of these compositeobjects has similar primary characteristics of a slope duration, andpolarity to the fundamental objects. However, for the composite objects,the characteristic of slope can comprise a time series characteristicgiven as a slope dataset. The composite object level also has thecharacteristic of “intervening interval time-series” defined by a timeseries of the intervals between the recognized or selected compositeobjects. At this level a wide range of discretionary indexcharacteristics can be derived from the comparison of basiccharacteristics of composite objects. Examples of such indexcharacteristics include: a “shape characteristic” as derived from anyspecified portion of the slope dataset of the object, a “positionalcharacteristic” as derived from, for example, the value of the lowest orhighest points of the object, or a “dimensional value characteristic” asderived by calculating the absolute difference between specified datapoints such as the value of the lowest and the highest values of theobject, or a “frequency characteristic” such as may be derived fromperforming a Fourier transform on the slope dataset of the object.

The next analysis level is called the “complex object level”. In thislevel, each sequential complex object comprises plurality of compositeobjects meeting specific criteria. A complex object has the samecategories of primary characteristics and derived index characteristicsas a composite object. A complex object also has the additionalcharacteristics of “composite object frequency” or “composite objectorder” which can be used as search criteria defined by a selectedfrequency or order of composite object types, which are specified asdefining a given complex object. A complex object also has additionalhigher-level characteristics defined by the time-series of the shapes,dimensional values, and positional characteristics of its componentcomposite objects. As described for the composite objects, similar indexcharacteristics of the complex objects can be derived from thesecharacteristics for example; a “shape characteristic” derived from themean rate of change along the dataset of the mean slopes of compositeobjects. Alternatively characteristics or index characteristics may becombined with others. For example, a shape characteristic may becombined with a frequency characteristic to provide a time series of amathematical index of the slopes and the frequencies of the compositeobjects.

The next level, termed the “global objects level” is then derived fromthe time series of complex objects. At this level global characteristicsare derived from the time series datasets of complex objects (and all oftheir characteristics). At the global objects level, the processor canidentity general specific patterns over many hours of time. An exampleof one specific pattern which is readily recognizable at this levelwould be a regular monotonous frequency of occurrence of onesubstantially complex object comprised of composite objects havingalternating polarities, each with progressively rising or falling slopedatasets. This pattern is typical of Cheyene-Stokes Respirations and isdistinctly different from the pattern typical of upper airwayinstability at this global object level. Additional higher levels can beprovided if desired as by a “comprehensive objects level” (not shown)which can include multiple overnight studies wherein a comprehensiveobject is comprised of a dataset of “global objects”.

While FIG. 3 b and FIG. 4 illustrate the levels of object derivations ofa ventilation signal, in another example a similar hierarchicalarchitecture can be derived for the timed data set of the pulse waveform(as from an arterial pressure monitor or the plethesmographic pulse).Here the fundamental level is provided by the pulse tracing itself andincludes all the characteristics such as ascending and descending slope,amplitude, frequency, etc. This signal also includes the characteristicof pulse area (which, if applied to a precise signal such as the flowplot through the descending aorta, is analogous to tidal volume in thefundamental minute ventilation plot). When the pulse signal isplethesmographic, it is analogous to a less precise signal ofventilation such as nasal pressure or thermister derived airflow. Withthese less precise measurements, because the absolute values are notreliable indicators of cardiac output or minute ventilation, the complexspatial relationships along and between signals become more importantthan any absolute value of components of the signal (such as absoluteamplitude of the ascending pulse or inspiration curve). In other word,the mathematical processing of multiple signals that are simply relatedto physiologic parameters (but are not a true measurement of thoseparameters) is best achieved by analyzing the complex spatialrelationships along and between those signals. To achieve this purpose,according to the present invention, as with ventilation, the pulsesignal is organized into a similar multi-level hierarchy of overlappingtime series of objects. Subsequently these are combined and comparedwith the processed objects of respiration to derive a unified objecttime series defined by multiple corresponding data sets.

FIG. 5 a shows an exemplary pathophysiologic process associated with acharacteristic dynamic pattern of interaction. As discussed previously,this cyclic process is induced by upper airway instability. FIG. 5 bshows four corresponding signals derived from monitoring differentoutputs of the patient during a time interval wherein the dynamicprocess of FIG. 5 a is operative. The basic signals shown are Pulse,Chest Wall Impedance, Airflow, and Oxygen Saturation (SPO2). Accordingto the present invention, these signals are processed into time seriesfragments (as objects) and organized into the object levels aspreviously discussed. For the purpose of organizing and analyzingcomplex interactions between these corresponding and/or simultaneouslyderived signals, the same basic ascending process is applied to eachsignal. As shown in FIG. 5 c these streaming objects, many of whichoverlap, project along a three-dimensional time series comprised ofmultiple levels of a plurality of corresponding signals. A “multi-signalobject” is comprised of at least one object from a first signal and atleast one object from another signal. The multi-signal object of FIG. 5c has the primary and index characteristics derived from each componentsignal and from the spatial, temporal, and frequency relationshipsbetween the component signals. As illustrated, the objects defining amulti-signal object can include those from analogous or non-analogouslevels. With this approach even complex and subtle dynamic patterns ofinteraction can be recognized.

This type of representation is too complex for presentation to hospitalpersonnel but is preferred for the purpose of general representation ofthe data organization because, at this level of complexity, a completerepresentation of the time series does not lend itself well to atwo-dimensional graphical (and in some cases a three dimensional)representation. Along the time series of sequential multi-signalobjects, the spatial characteristics of these multi-signal objectschange as a function of a plurality of interactive and differentcharacteristics derived from the different signals.

The mathematical power of this approach to characterize the achievedorganization of the complexity of the timed behavior of a physiologicsystem is illustrated by the application of this method to characterizethe codependent behavior of ventilation and arterial oxygen saturationand plethesmographic pulse. While these variables are codependent inthat a chance in one variable generally causes a change in the othertwo. They are also each affected differently by different pathologicinsults and different preexisting pathologic changes. For example, themulti-signal objects comprising a time series of ventilation andarterial oxygen saturation and plethesmographic pulse in a sedated50-year-old obese smoker with asthma and sleep apnea are very differentthan those of a sleeping 50 year-old patient with Cheyene StokesRespiration and severe left ventricular dysfunction. These differencesare poorly organized or represented by any collection of two-dimensionalgraphical and/or mathematical representations. Despite this, throughoutthis disclosure, many of the signal interactions (such as those relatingto pathophysiologic divergence) will be discussed as a function of asimplified two-dimensional component representation for clarity based onolder standards of mathematical thought. However, it is one of theexpress purposes of the present invention to provide a much moremathematical robust system for the organization and analysis of thecomplex mathematical interactions of biologic systems through theconstruction of time series sets of multidimensional and overlappingobjects.

To illustrate the complexity ordered by this approach, consider thecomponents of just one of the three simple recovery objects shown inFIGS. 5 b and 5 c. This single recovery object includes the followingexemplary characteristics, each of which may have clinical relevancewhen considered in relation to the timing and characteristics of otherobjects;

-   -   1. Amplitude, slope, and shape of the oxygen saturation rise        event at the composite level.    -   2. Amplitude, slope, and shape of the ventilation rise event at        the composite level which contains the following characteristics        at the fundamental level;        -   Amplitude, slope, and shape of the inspiration rise object        -   Amplitude, slope, and shape of the expiration fall object.        -   Frequency and slope dataset of the breath to breath interval            of tidal breathing objects        -   Frequency and slope data sets of the amplitude, slope, and            shape of the pulse rise and fall events    -   3. Amplitude, slope, and shape of the pulse rise event at the        composite level which contains the following exemplary        characteristics at the fundamental level;        -   Amplitude, slope, and shape of the plethesmographic pulse            rise event.        -   Amplitude, slope, and shape of the plethesmographic pulse            fall event.        -   Frequency and slope datasets of beat-to-beat interval of the            pulse rate.        -   Frequency and slope data set of the amplitude, slope, and            shape of the pulse rise and fall events

As is readily apparent, it is not possible for a health care worker totimely evaluate the values or relationships of even a modest traction ofthese parameters. For this reason the output based on the analysis ofthese time series of objects are presented in a succinct andinterpretive format as still be discussed.

FIGS. 6 a-6 d shows one example of a presently preferred method foranimation of the summarized relationships between multiple interactingobjects on the hospital monitor display. Such an animation can be shownas a small icon next to the real-time numeric values typically displayedon present monitors. Once the baseline is established for a patienteither for example as the patient's baseline settings for a selected orsteady state time period (of for example 10-15 minutes) or by a selectedor calculated set of normal ranges, this is illustrated as a square.(The patient may initially have parameters out of the normal ranges andnever exhibit a square output). After the square for this patient isestablished, the cube is built from the evolving time series of theseparameters. A given region of the cube can be enlarged or reduced as theparticular value monitored increases or decreases respectively. Therelationship between these variables can be readily seen even if theyremain within the normal range. The computer can flag with a redindicator a cube that is showing pathophysiologic divergence whencompared with the baseline values even though none of the values are ata typical alarm threshold. If other abnormalities (such as thedevelopment of pulse irregularity or a particular arrhythmia or STsegment change, this can be flagged on the cube so that the onset ofthese events can be considered in relation to other events. If preferredthe time series components of the cube and their relationships tooccurrences on other monitored time series can be provided in a twodimensional timeline.

Using this approach the time series relationships of multiplephysiologic events can be characterized on the screen with a smalldynamic animated icon in a succinct and easily understood way. There aremany other alternative ways to animate a summary of the dynamicrelationships and some of these will be discussed later in thedisclosure.

One of the longstanding problems associated with the comparison ofoutputs of multiple sensors to derive simultaneous multiple time seriesoutputs for the detection of pathophysiologic change is that theaccuracy and/or output of each sensor may be affected by differentphysiologic mechanisms in different ways. Because of this, the value ofmatching an absolute value of one measurement to an absolute value ofanother measurement is degraded. This is particularly true if themeasurement technique or either of the values is imprecise. For example,when minute ventilation is measured by a precise method such as apneumotachometer, then the relationship between the absolute values ofthe minute ventilation and the oxygen saturation are particularlyrelevant. However, if minute ventilation is being trended as by nasalthermister or nasal pressure monitoring or by chest wall impedance thenthe absolute values become much less useful. However, according to oneaspect of the present invention, the application of the slope dipolemethod, the relationship between a plurality of simultaneously derivedsignals can be determined independent of the relationships of theabsolute values of the signals. In this way, simultaneously derivedsignals can be identified as having convergence consistent withphysiologic subordination or divergent shapes consistent with thedevelopment of a pathologic relationship or inaccurate data acquisition.

As noted, with physiologically linked signals a specific occurrence ormagnitude of change in one signal in relationship to such a change inanother signal may be more important and much more reproducible than theabsolute value relationships of the respective signals. For this reason,the slope dipole method provides an important advantage to integratesuch signals. Using this signal integration method, two simultaneouslyacquired physiologic linked signals are compared by the microprocessorover corresponding intervals by matching the respective slope dipolesbetween the signals. Although the exact delay between the signals maynot be known, the processor can identity this by identifying the bestmatch between the dipole sets. In the preferred embodiment, this “bestmatch” is constrained by preset limits. For example, with respect toventilation and oximetry, a preset limit could be provided in the rangeof 10-40 seconds although other limits could be used depending on thehardware, probe site and averaging, intervals chosen. After the bestmatch is identified, the relationships between the signals are compared(for example, the processor can compare the slope dipole time series ofoxygen saturation to the slope dipole time series of an index of themagnitude of ventilation). In this preferred embodiment, each slopedipole is compared. It is considered preferable that the dipoles of eachrespective parameter relate to a similar duration (for example. 1-4seconds). With respect to airflow, calculation of the magnitude value ofairflow may require sampling at a frequency of 25 hertz or higher,however, the sampling frequency of the secondary plot of the magnitudevalue of the index can, for example, be averaged in a range of one hertzto match the averaging interval of the data set of oxygen saturation.Once the signals have been sufficiently matched at the dipole level thencan be further matched at the composite level According to the presentinvention, most object matching across different signals is performed atthe fundamental level or higher, however timing matching can beperformed at the dipole level and this can be combined with higher levelmatching to optimize a timing match. FIGS. 9, 10, and 11, show schematicmapping of matched clusters of airway instability (of the type shown inFIG. 5 b) where clusters are recognized and their components matched atthe composite object level. When the objects are matched, the baselinerange relationship between the signals can be determined. This baselinerange relationship can be a magnitude value relationship or a sloperelationship. The signals can then be monitored for variance from thisbaseline range, which can indicate pathology or signal inaccurate. Thevariance from baseline can be, for example, an increase in the relativevalue of ventilation in relation to the oximetry value or a greater rateof fall in oxygen saturation in relation to the duration and/or slope offall of ventilation. In another example, the variance can include achange from the baseline delay between delta points along the signals.

With multiple processed signals as defined above, the user, which can bethe program developer, can then follow the following to complete theprocess of searching for a specific pattern of relationships between thesignals.

-   -   1. Specify a search wave pattern    -   2. Analyze and divide the search pattern into objects    -   3. Input the allowed deviation (if any) from the search pattern        or the objects comprising it.    -   4. Input additional required relationships (if any) to other        objects in the target waveform    -   5. Apply the search pattern or selected component objects        thereof to a target waveform.

Various methods of identification may be employed to provide a wavepattern to the system. Users may:

-   -   Choose from a menu of optional patterns    -   Select dimensional ranges for sequential related patterns of        ascending complexity    -   Draw a wave pattern within the system with a pointing or pen        device    -   Provide a scanned waveform    -   Provide a data feed from another system    -   Describe the pattern in natural language    -   Type in a set of points    -   Highlight a sub-section of another waveform within the system

The system can be automated such that such a search is automaticallyapplied once the criteria are established. Also the method ofidentification of the search pattern can be preset. For example theoccurrence of a specific sequence of objects can be used as a trigger toselect a region (which can be one of those objects) as the specifiedsearch pattern, the processor can automatically search for other suchpatterns in the rest of the study. The result of any of these inputswould be a set of points with or without a reference coordinate systemdefinition as shown in FIGS. 3 a-3 h.

The system now begins its analysis of the target set of points to derivea series of object sets. These sets will be used to identify keyproperties of the wave pattern. These objects (and their boundaries)will provide a set of attributes which are most likely to be significantin the wave pattern and that can be acted upon in the following ways:

-   -   To provide parameters on which sets of rules may be applied for        the identification of expected conditions    -   To provide parameters that can be associated with specifically        allowable deviations and/or a globally applied deviations    -   To provide parameters than can be used to score the relative        similarity of patterns within the target waveform

Using this method, a search can be carried out for specificpathophysiologic anomalies. This can be carried out routinely by thesoftware or on demand.

One example of the clinical utility of the application of the objectprocessing and recognition system to physiologic signals is provided byidentification of upper airway instability. As discussed in theaforementioned patents and application, events associated with airwayinstability are precipitous. In particular, the airway closure isprecipitous and results in a rapid fall in ventilation and oxygensaturation. Also the subsequent airway opening airway is precipitous,and because ventilation drive has risen during closure the resultingventilation flow rate (as represented by a measurement of airflowdeflection amplitude) rises rapidly associated with recovery. Also,after the period of high flow rate associated with the recovery the flowrate precipitously declines when the chemoreceptors ol the brain senseventilation overshoot. In this way, along a single tracing of timedairflow deflection amplitude, three predictable precipitous relativelylinear and unidirectional waveform deflections changes have occurred ina particular sequence in a manner analogous to the tracing of the SpO₂or pulse rate. Subsequent to this, the unstable airway attain closessuddenly propagating the cluster of cycles in all of these waveforms.

As noted above, a hallmark of airway instability is a particular clustertimed sequence of precipitous, unidirectional changes in the timed dataset. For this reason, the first composite object to be recognized isdefined by a precipitous unidirectional change in timed output of one ofthe above parameters. The system then recognizes along the fundamentalsequential unipolar composite objects and builds the composite levelcomprised of time series of these composite objects. One presentlypreferred embodiment uses the following method to accomplish this task.A unipolar “decline object” is a set of consecutive points over whichthe parameter level of the patient is substantially continually falling.A unipolar “rise object” is a set of consecutive points over which theparameter is substantially continually increasing. A “negative pattern”is a decline together with a rise object wherein the rise follows thedecline within a predetermined interval. A “positive pattern” is a risetogether with a decline wherein the decline follows the rise within apredetermined interval. How closely these composite objects can followeach other is a specifiable parameter. At the complex object level, acluster is a set of consecutive positive or negative patterns thatappear close together. How closely these patterns must follow each otherto qualify, as a cluster is a specifiable parameter. (Typical ranges forthese parameters have been discussed in the aforementioned patents).

When applied, the digital pattern program proceeds in several phases. Inthe first phase, decline and rise objects are identified. In the secondphase, negative and positive patterns are identified. In the thirdphase, clusters of negative and/or positive patterns are identified inthe fourth phase of the relationship between the events and patterns iscalculated and outputted. In the fifth phase a diagnosis and severityindexing of airway or ventilation instability or sleep/sedation apnea ismade, in the sixth phase a textual alarm or signal is outputted and/ortreatment is automatically modified to eliminate cluster, then theprocess is then repeated with each addition to the dataset in real-timeor with stored timed datasets.

The presently preferred system applies either a linear or iterativedipole slope approach to the recognition of waveform events. Since theevents associated with airway collapse and recovery are generallyprecipitous and unipolar, the linear method suffices for the recognitionand characterization of these nonlinear waves. However the iterativedipole slope approach is particularly versatile and is preferred insituations wherein the user would like an option to select theautomatically identification of a specific range of nonlinear or morecomplex waves. Using the iterative dipole slope method, the user canselect specific consecutive sets of points from reference cases along awaveform as by sliding the pointer over a specific waveform region.Alternatively, the user can draw the desired target waveform on a scaledgrid. The user can also input or draw range limits thereby specifying anobject or set of objects for the microprocessor to recognize along theremainder of the waveform or along other waveforms. Alternatively theprocessor can automatically select a set of objects based onpre-selected criteria (as will be discussed). Since the iterative dipoleprocess output is shape (including frequency and amplitude) dependentbut is not necessarily point dependent, it is highly suited to functionas a versatile and discretionary engine for performing waveform patternsearches. According to the present invention, the waveform can besearched by selecting and applying objects to function as BooleanOperators to search a waveform. The user can specify whether theseobjects are required in the same order. Recognized object sequencesalong the waveform can be scored to shoes the degree of match with theselected range. If desired (as for research analysis of waveformbehavior) anomalies within objects or occurring in one or more of aplurality of simultaneously processed tracings can be identified andstored for analysis.

For the purpose of mathematically defining the presently preferredobject system, according to the present invention, for recognition ofdigital object patterns let o₁, o₂, . . . , o_(m) be the original datapoints. The data can be converted to a smoother data set, x₁, x₂, . . ., x_(n), by using a moving n average of the data points as a 1-4 secondaverage for cluster recognition or as a 15-30 second average for theidentification of a pathophysiologic divergence. For the sake of clarityof presentation, assume that x, is the average of the original datapoints for the i^(th) second. A dipole is defined to be a pair ofconsecutive data points. Let d_(i)=(x_(i),x_(i+1)) be the i^(th) dipole,for i=1,2, . . . , n−1. The polarity, say p_(i) of the i^(th) dipole isthe sign of x_(i+1)−x_(i), (i.e. p_(i)=1 if x_(i+1)>x_(i), p_(i)=0 ifx_(i+1)=x_(i), and p_(i)=−1 if x_(i+1)<x_(i)) For the purpose ofautomatic recognition of user specified, more complex nonlinearwaveforms, the data can be converted to a set of dipole slopes, z₁, z₂,. . . , z_(n),. Let z_(i)=(x_(i+1−)x_(i),) be the i^(th) dipole slope,for i=1, 2, . . . , n−1.

To recognize a decline event by applying the iterative slope dipolemethod according to the present invention, Let, {z₁, z₂, . . . , z_(n)}be a set of consecutive dipole slopes. Then {z₁, z₂, . . . , z_(n)} is adecline if it satisfies the following conditions:

-   -   1. z₁,z₂, . . . , z_(n) are less than zero i.e., the parameter        level of the patient is continually falling over the set of        dipole slopes. (This condition will be partially relaxed to        adjust for outliers, as by the method described below for the        linear method.)    -   2. the relationship of Z_(i) to z₂, z₂ to z₃, . . . z_(n−1) to        z_(n) is/are specified parameter(s) defining the shape of the        decline object, these specified parameters can be derived from        the processor based calculations of the dipole slopes made from        a user selected consecutive data set or from a set drawn by the        user onto a scaled grid.

To recognize a rise event a similar method is applied wherein z₁, z₂, .. . , z_(n) are greater than zero. Complex events, which include riseand fall components are built from these more composite objects.Alternatively, a specific magnitude of change along a dipole slopedataset can be used to specify a complex object comprised of twocomposite objects separating at the point of change (a waveformdeflection point). In one application the user slides the cursor overthe portion of the wave, which is to be selected, and this region ishighlighted and enlarged and analyzed with respect to the presence ofmore composite objects. The dimensions of the object and the slope dataset, which defines it, can be displayed next to the enlarged waveform.If the object is complex (as having a plurality of segments of differingslope polarity or having regions wherein the slope rapidly changes as bya selectable threshold) then each composite object is displayedseparately with the respective dimensions and slope data sets. In thisway the operator can confirm that this is the actual configurationdesired and the user is provided with a summary of the spatial anddimensional characteristics of the composite objects, which define theactual selected region. The operator can select a range of variations ofthe slope data set or chance the way in which the composite objects aredefined, as by modifying the threshold for a sustained change in slopevalue along the slope dataset. (For example, by allotking at least oneportion of the slopes to vary by a specified amount, such as 10%, byinputting graphically the variations allowed. If the operator “OKs” thisselection, the processor searches the entire timed dataset for thecomposite objects, building the selected object from the compositeobjects if identified

To recognize a decline event by applying the linear method according tothe present invention. Let {x_(i),x_(i+1), . . . , x_(r)} be a set ofconsecutive points and let s=(x_(r)−x_(d)/(r−i) be the overall slope ofthese points. (The slope could be defined by using linear regression,but this presently preferred definition allows for improved fidelity ofthe output by allotting rejection based on outlier identification, whichwill be discussed). Then {x_(i), x_(i+1), . . . x_(r)} is a decline ifit satisfies the following conditions:

-   -   3. x_(i)>x_(i+1) 2> . . . x_(r), i.e. the parameter level of the        patient is continually falling over the set of points. (This        condition will be partially relaxed to adjust for outliers, as        described belong.)    -   4. r−i≧D_(min), where D_(min) is a specified parameter that        controls the minimum duration of a decline.    -   5. s_(min)≦s≦s_(max), where s_(min) and s_(max) are parameters        that specify the minimum and maximum slope of a decline,        respectively.

The set {97, 95, 94, 96, 92, 91, 90, 88}, does not satisfy the currentdefinition of a decline even though the overall level of the parameteris clearly falling during this interval. The fourth data point, 96, isan outlier to the overall pattern. In order to recognize this intervalas a decline, the first condition must be relaxed to ignore outliers.The modified condition 1 is:

-   -   1*. Condition 1 with Outlier Detection    -   a. x_(i)>x_(i+1),    -   b. x_(i)>x_(i+1) or x_(i+1)>x_(j+2) for j=i+1, . . . , r−2.    -   c. x_(r−1)>x_(r).

To recognize a rise event, let {x_(i), x_(i+1), . . . , x_(r)} be a setof consecutive points and let s=(x_(r)−x_(i)/(r−i) be the overall slopeof these points. Then {x_(i), x_(i+1), . . . , x_(r)} is a rise if itsatisfies the following conditions:

-   -   1. x_(i)<x_(i+1)< . . . <x_(r), i.e., the parameter level of the        patient is continually rising over the set of points. (This        condition will be partially relaxed to adjust for outliers, as        described below.)    -   2. r−i≧D_(min), where D_(min) is a specified parameter that        controls the minimum duration of rise.    -   3. s_(min)≦s≦s_(max), where s_(min) and s_(max) are parameters        that specify the minimum and maximum slope of a decline,        respectively.

Similar to declines, the first condition of the definition of a rise isrelaxed in order to ignore outliers. The modified condition 1 is:

-   -   1*. Condition 1 with Outlier Detection    -   a. x_(i)<x_(i+1).    -   b. x_(j)<x_(j+1) or x_(j+1)<x_(j+2) for j=i+1, . . . , r−2.    -   c. x_(r−1)<x_(r).

To recognize a negative pattern the program iterates through the dataand recognize events and then identifies event relationships to definethe patterns. The system uses polarities (as defined by the direction ofparameter movement in a positive or negative direction) to test forcondition (1*) rather than testing for greater than or less than. Thissimplifies the computer code by permitting the recognition of alldecline and rise events to be combined in a single routine and ensuresthat decline events and rise events do not overlap, except that they mayshare an endpoint. The tables below show how condition (1*) can beimplemented using polarities. Equivalent Condition 1* for Decline eventCondition 1* Equivalent Condition a. x_(i) > x_(i−1) p_(i) = −1 b.x_(i) > x_(j−1) or x_(j−1) > x_(j−2) p₁ = −1 or p_(j+1) = −1 c.x_(r−1) > x_(r) p_(r−1) = −1

Equivalent Condition 1* for Rise event Condition 1* Equivalent Conditiona. x_(i) < x_(i 1) p_(i) = 1 b. x_(i) < x_(j−1) or x_(j−1) < x_(j−2) p₁= 1 or p_(j+1) = 1 c. x_(r−1) < x_(r) p_(r−1) = 1

The pseudocode for the combined microprocessor method, which recognizesboth unipolar decline events and unipolar rise events, is shown below.In this code, E is the set of events found by the method, where eachevent is either a decline or a rise. Event Recognition i = 1exent_polarity = p₁ for j = 2 to n−2 if (p_(i) ≠ event_polarity) and(p_(i−1) ≠ event_polarity) r = j X = ¦x_(p)....x_(r)¦ if event_polarity= 1 Add X to E if it satisfies rise conditions (2) and (3) elseifevent_polarity = −1 Add X to E if it satisfies decline conditions (2)and (3) endif i = j event_polarity = p_(i) endif

-   -   endfor    -   Add X={x_(i), . . . , x_(n)} to E if it satisfies either the        rise or decline conditions

Next, A specific pattern is recognized by identifying a certain sequenceof consecutive events, as defined above, which comply with specificspatial relationships. For example, a negative pattern is recognizedwhen a decline event, say D={x_(i), . . . , x_(j)}, together with a riseevent, say R={x_(k), . . . , x_(m)}, that closely follows it. Inparticular, D and R must satisfy k−i≦t_(dr), where t_(dr) is aparameter, specified by the user, that controls the maximum amount oftime between D and R to qualify as a negative pattern.

The exemplary pseudocode for the microprocessor system to recognize anegative pattern is shown below. Let E={E₁,E₂, . . . , E_(q)} be the setof events (decline events and rise events) found by the eventrecognition method, and let DR be the set of a negative pattern.Negative Pattern Recognition for h = 1 to q−1 Let D = {x_(i),...,x_(j),}be the event E_(h) if D is a decline event Let R = {x_(k),...,X_(m)} bethe event E_(h+1) if R is a rise event gap = k − j if gap ≦ t_(dr) Add(D,R) to the list. DR of negative patterns endif endif endif endfor

As noted, a cluster is a set of consecutive negative or positivepatterns that appear close together. In particular, letC={DR_(i),DR_(i+1), . . . , DR_(k)} be a set of consecutive negativepatterns. s_(j) be the time at which DR_(j) starts, and e_(j) be thetime at which DR_(j) ends. Then C is a cluster if it satisfies thefollowing conditions:

-   -   1. s_(j+1)−e_(j)≦t_(c), for j=i, . . . , k−1, where t_(c) is a        parameter, specified by the user, that controls the maximum        amount of time between consecutive negative patterns in a        cluster.    -   2. k−i−1≧c_(min), where e_(min) is a parameter, specified by the        user, that controls the minimum number of negative patterns in a        cluster.

The pseudocode for the algorithm to recognize clusters of negativepatterns is shown below. Let DR={DR₁, DR₂, . . . , DR_(r)} be the set ofnegative patterns found by the above pattern recognition method. ClusterRecognition (of negative patterns) f = 1: for h = 2:r Let R =¦x_(l),.....x_(m)¦ be the rise in DR_(h−1) Let D = ¦x_(i),.....x_(j)¦ bethe decline in DR_(h) gap = i − m if gap > t_(c) g = h − 1 if g − f + 1≧ c_(min) Add DR_(l)· DR_(i·1)...., DR_(g) to the list of clusters endiff = h endif endfor g = r if g − f − 1 ≧ c_(min) Add DR_(i − DR)_(i−1)..... DR_(g) to the list of clusters endif

According to the present invention, this object based linear method mapsthe unique events, patterns and clusters associated with airwayinstability because the sequential waveform events associated withairway closure and reopening are each both rapid, substantially unipolarand relatively linear. Also the patterns and clusters derived arespatially predictable since these precipitous physiologic changes arepredictably subject to rapid reversal by the physiologic control system,which is attempting to maintain tight control of the baseline range.Because timed data sets with predictable sequences of precipitousunidirectional deflections occur across a wide range of parameters, thesame digital pattern recognition methods can be applied across a widerange of clustering outputs, which are derived from airway instability.Indeed the basic underlying mechanism producing each respective clusteris substantially the same (e.g. clusters of positive pulse ratedeflections or positive airflow amplitude deflections). For this reason,this same system and method can be applied to a timed data set of theoxygen saturation, pulse rate (as for example determined by a beat tobeat calculation), amplitude of the deflection of the chest wallimpedance waveform per breath, amplitude of deflection of the airflowsignal per breath (or other correlated of minute ventilation), systolictime intervals, blood pressure, deflection amplitude of the nasalpressure, the maximum exhaled CO2 per breath, and other signals.Additional details of the application of this digital patternrecognition method to identify clusters are provided in patentapplication Ser. No. 09/409,264 to the present inventor.

Next, for the purpose of building the multi-signal object, a pluralityof physiologically linked signals are analyzed for the purpose ofrecognizing corresponding patterns and corresponding physiologicconvergence for the optimal identification of the cluster cycles. Forexample, a primary signal such as airflow is analyzed along with acontemporaneously measured secondary signal such as oxygen saturation asby the method and system discussed previously. As discussed previously,for the purpose of organizing the data set and simplifying the analysis,the raw airflow signal is processed to a composite object level. Forexample, the composite level of airflow can be a data set of theamplitude and/or frequency of the tidal airflow as by thermister orpressure sensor, or another plot, which is indicative of the generalmagnitude of the timed tidal airflow. In the presently preferredembodiment, a mathematical index (such as the product) of the frequencyand amplitude is preferred, because such an index takes into account theimportant attenuation of both amplitude and frequency during obstructivebreathing. Furthermore, both the frequency and amplitude are oftenmarkedly increased during the recovery interval between apneas andhypopneas. It is not necessary that such a plot reflect exactly the truevalue of the minute ventilation but rather, it is important that theplot reflect the degree of change of a given level of minuteventilation. Since these two signals are physiologically linked, anabrupt change in the primary signal (airflow) generally will producereadily identifiable change in the subordinate signal (oxygensaturation). As previously noted, since the events which are associatedwith airway collapse are precipitous, the onset of these precipitousevents represent a brief period of rapid change which allows for optimaldetection of the linkage between the primary signal and the subordinatesignal.

The signals can be time matched by dipole slopes at the fundamentallevel. In addition, in one preferred embodiment, the point of onset ofprecipitous change is identified at the composite object level of theprimary signal and this is linked to a corresponding point of aprecipitous change in the composite object level of the subordinatesignal. This is referred to herein as a delta point. As shown in FIGS.9, 10, and 11, a first delta point is identified in the primary signaland in this example is defined by the onset of a rise object. Acorresponding first delta point is identified in the subordinate signaland this corresponds to the onset of a rise object in the subordinatesignal. A second delta point is identified which is defined by the pointof onset of a fall object in the primary signal and which corresponds toa second delta point in the subordinate signal defined by the onset of afall event in the secondary signal. The point preceding the second deltapoint (the “hyperventilation reference point”) is considered a referenceindicating an output associated with a degree of ventilation, whichsubstantially exceeds normal ventilation and normally is at least twicenormal ventilation. When applying airflow as the primary signal andoximetry as the subordinate signal, the first delta point match is themost precise point match along the two integrated waveforms andtherefore comprises a (“timing reference point”) for optimally adjustingfor any delay between the corresponding objects of the two or moresignals. The mathematical aggregate (such as the mean) of an index ofthe duration and slope, and/or frequencies of composite rise and fallobjects of the fundamental level of tidal ventilation along a shortregion adjacent these reference points can be applied as a generalreference for comparison to define the presence of relative levels ofventilation within objects along other portions of the airflow timeseries. Important fundamental object characteristics at these referencepoints are the slope and duration of the rise object or fall objectbecause these are related to volume of air, which was moved during thetidal breath. The fundamental objects comprising the tidal breaths atthe reference hyperventilation point along the composite level areexpected to have a high slope (absolute value) and a high frequency. Inthis way both high and low reference ranges are determined for thesignal. In another preferred embodiment, these points can be used toidentify the spatial shape configuration of the rise and fall objects atthe fundamental level during the rise and fall objects at the compositelevel.

As shown in FIGS. 9 and 10, using this method at the composite objectlevel, a first object (FIG. 11) can then identified in the primarysignal between the first delta point and the second delta point which isdesignated a recovery object. As also shown in FIG. 11 the matchedrecovery object is also identified in the subordinate signal as thepoint of onset of the rise object to the point of the onset of the nextsubsequent fall object. In the preferred embodiment, the recovery objectis preceded by the apnea/hypopnea object which is defined by the pointof onset of the fall object to the point of onset of the next riseobject in both the primary and subordinate signals.

As shown in FIG. 12, a recovery object recognized at the composite levelcan used to specify a region for comparison of sequential objects at thefundamental object level. Here, upon recognition of the presence of arecovery object (where it is anticipated that the ventilation effortwill be high) the ratio of the slope of exhalation objects to the slopeof inhalation objects can be compared within the recovery object and thetime series derived from these comparisons can be plotted if desired.During upper airway obstruction, the inspiration is slowed to a greaterdegree than exhalation. The magnitude change of the ratio during theclusters of apneas provides an index of the magnitude of upper airwaynarrowing (which selectively slows inhalation during the clusteredapnea/hypopnea objects). However, during the recovery object or at the“hyperentilation reference point”, the upper airway should be wide openfor both inhalation and exhalation and this can be used as a referencebecause, during this time,. The absolute slope of the fundamentalobjects during recovery can then be compared to the absolute slope ofthe fundamental objects during other times along the night to provide anindication of upper or looser airway narrowing.

When airflow is the primary signal and oximetry the subordinate, themost reliable delta point is the point of onset of a rapid rise inventilation (in a patient with an oxygen saturation, at the point ofonset point, of less than 96-97%). Patients with very unstable airwayswill generally have relatively short recovery objects. Other patientswith more stable airways may have a multi-phasic slope of decline inairflow during the recovery objects herein, for example, there is aninitial precipitous decline event in the airflow parameter and then aplateau or a much more slight decline which can be followed by a secondprecipitous decline to virtual absence of ventilation. Using the slopedipole method these composite objects can be readily separated such thatthe occurrence of multiple composite objects (especially wherein theslopes are close to zero) or a single object Faith a prolonged slowlyfalling slope dataset occurring immediately after the first data point,can be identified. These patients generally have longer recoveryintervals and more stable airways. The identification of a declineobject associated with decline from the hyperventilation phase ofrecovery followed by a plateau and/or a second decline object associatedwith the onset of apnea is useful to indicate the presence of a greaterdegree of airway stability. Accordingly, with the airflow signal, athird delta point (FIG. 12) designated a “airflow deflection point” canoften be identified in the airflow tracing corresponding to thedeflection point at the nadir of drop in airflow at the end of therecovery. This point is often less definable than the second delta pointand for this reason matching the second delta points in the airflow andoximetry signals is preferred although with some tracings a matchbetween the airflow deflection point and the second delta point in theoximetry dataset provides a better match.

If a significant decline in airflow is identified after the “airflowdeflection point” then the region of the intervening decline object andthe next delta point (onset of the next recovery) is designated areference “ventilation nadir region”. If the region or object(s) fromthe second delta point to ventilation deflection point is very short (as0-3 breaths) and the ventilation nadir region has a mean slope close toor equal to zero (i.e. the region is relatively flat) and the deflectionamplitude is close to zero or otherwise very small indicating now orvery little ventilation, then the airway is designated as highlyunstable.

Another example of object processing at the fundamental object level,according to the present invention, includes the processor-basedidentification of fluttering of the plateau on the pressure signal torecognize partial upper airway obstruction. During the nasal pressuremonitoring a fluttering plateau associated with obstructive breathingoften occurs intervening a rise event and a fall event of tidalbreathing. Since the plateau objects are easily recognizable at thefundamental level and readily separated using the present objectrecognition system the plateau can be processed for the tiny rise andfall objects associated with fluttering and the frequency of theseobjects can be determined. Alternatively, a Fourier transform can beapplied to the plateau objects between the rise and fall events of thenasal pressure signal to recognize the presence of fluttering or anothermethod can be utilized which provides an index of the degree offluttering of the plateau objects.

Since reduced effort also lowers the slope of exhalation andinspiration, the configuration (as defined by the slope dataset of thedipoles defining the fundamental objects of both inspiration andexpiration at the reference objects) can be applied as referencefundamental object configurations defining the presence ofhyperventilation or hypopnea. This process is similar to the selectionprocess for identifying search objects described earlier but in thiscase the input region is pre-selected. In an example, the range ofcharacteristics of the objects at the fundamental level derived from oneor more tidal breaths occurring prior to the second airflow delta pointcan be used to designate a reference hyperventilation objects range.Alternatively the object based characteristics, defined by of the rangeof characteristics of the objects derived from one or more tidal breathsoccurring prior to the first airflow delta point can be used designate areference hypopnea objects range. The processor can then automaticallyassess object ranges along other points of the tracing. In this way theprocessor can apply an artificial intelligence process to theidentification of hypopneas by the following process:

-   -   1. Identify the region wherein a hypopnea is expected (as for        example two to three tidal breaths prior to the first airflow        delta point).    -   2. Select this as a region for objects processing to define the        characteristics of hypopneas in this patient.    -   3. Process the region using the slope dipole method to define        the range of fundamental objects comprising the target region.    -   4. Compare the identified range of objects to other analogous        objects along to tracing to identify new objects having similar        characteristics.    -   5. Using the criteria derived from the objects defining the        target region search the processed waveform for other regions        having matching sequences of new objects and identify those        regions.    -   6. Provide an output based on said identification and/or take        action (e.g. increase CPAP) based on said identification.

These processing methods exploit the recognition that certain regionsalong a multi-signal object (as within a cluster) have a very highprobability of association with certain levels of ventilation. Theobjects defining those regions can then be used as a reference or as anopportunity to examine for the effects of a given level of ventilationeffort on the flow characteristics. Patients with obstructive sleepapnea will have a fall in the slopes of fundamental inspiration objectsduring decline objects at the composite level indicative of upper airwayocclusion. Also, as shown in FIG. 12, patients with asthma or chronicobstructive lung disease will have a reduced slope of the exhalationwhen compared to the slope of inhalation during the rise objects betweenapneas at the base level. According one embodiment of the presentinvention, the time series of the ratio of the slope of inhalationobjects to exhalation objects is included with the basic time series.Patients with simple, uncomplicated obstructive apnea will have clustersof increasing slope ratios with the ratio rising to about one during therecovery objects. Patients with combined obstructive apnea and asthma orchronic obstructive lung disease will have a greater rise in sloperatios during the recovery objects to into the range of 2-3 or greater,indicating the development of obstructive lower airways during the rapidbreathing associated with recovery.

One presently preferred system for processing, analyzing and acting on atime series of multi-signal objects is shown in FIG. 8. The examplesprovided herein show the application of this system for real timedetection, monitoring, and treatment of upper airway and ventilationinstability and for the timely identification of pathophysiologicdivergence. The system includes a portable bedside processor 10preferably having at least a first sensor 20 and a second sensor 25,which preferably provide input for at least two of the signals discussedsupra. The system includes a transmitter 35 to a central proccssing unit37. The bedside processor 10 preferably includes an output screen 38,which pros ides the nurse with a bedside indication of the sensoroutput. The bedside processors can bc connected to a controller of atreatment or stimulation device 50 (which can include a positivepressure delivery device, an automatic defibrillator, a vibrator orother tactile stimulator, or a drug delivery system such as a syringepump or back to the processor to adjust the analysis of the time-seriesinputs), the central unit 37 preferably includes as output screen 55 andprinter 60 for generating a hard copy for physician interpretation.According to present invention, as will be discussed in detail, thesystem thereby allows recognition ol airway instability, complicationsrelated to such instability, and pathophysiologic divergence in realtime from a single or multiple inputs. The bedside processor ispreferably connected to a secondary processor 40 which can be a unit,which performs measurements intermittently and/or on demand such as anon-invasive blood pressure monitor or an ex-vivo monitor, which drawsblood into contact with a sensor on demand for testing to derive datapoints for addition to the multi-signal objects. The secondary monitor40 includes at least one sensor 45. The output of the bedside processorcan either be transmitted to the central processor 37 or to the bedsidemonitor 10 to render a new object output, action, or analysis.

The method of hypopnea recognition discussed previously can be coupledwith a conventional CPAP auto titration system which can comprise onetreatment device of FIG. 8 improve CPAP titration. The previouslydescribed method for detecting hypopneas is particularly useful toidentify milder events because, while the configuration of each tidalbreath of within the hypopnea may be only mildly different, there is acumulative decline in ventilation or increase in airway resistance whichoften, eventually directly triggers a recovery object or triggers anarousal which then triggers the occurrence of a recovery object. Therecovery objects being a precipitous response to a mild but cumulativedecline on airflow is easier to recognize and is exploited to specifytiming of the target processing as noted above.

One of the problems with conventional CPAP is that many of them (if notall) operate with pre-selected criteria for recognition of a hypopnea(such as 50% attenuation of a breath or group of breaths when comparedwith a certain number of preceding breaths.). These systems generallydetermine the correct pressures for a given patient by measuringparameters derived from the algorithms which monitor parameters throughthe nasal passage. Unfortunately, the nasal passage resistance is highlyvariable from patient to patient and may be variable in a single patientfrom night to night. These simplistic single parameter systems are evenless system is less suitable in the hospital where many confoundingfactors (such as sedation, etc.) may severely affect the performance ofconventional auto titration system. Since most auto-titration systemmonitors their effectiveness through nasal signals their algorithms arelimited by this wide variability of nasal resistance from patient topatient. Studies have shown that, while apneas can be detected, thedetection of hypopneas by these devices is often poor. This becomes evenmore important for the detection of mild hypopneas, which can be verydifficult to reliably detect (without an unacceptably high falsepositive rate) through a nasal signal alone. Indeed these milderhypopneas are more difficult characterize and not readily definable as aset of function of a set of predetermined rules for general applicationto all patients.

One preferred process of applying the system of FIG. 8 to customizehypopnea recognition to match a given patients nasal output isrepresented in FIG. 17. The present invention includes an auto titrationsystem, which adjusts its titration algorithm (which can be any of theconventional algorithms) based on the configurations of the multi-signalobject, which can include oximetry, chest wall movement, or EEG datasets. With this system, for example, the initial titration algorithm isapplied with the data set of CPAP pressure becoming part of themulti-signal object. The object time series at the composite level ismonitored for the presence of persistent clusters (especially clusteredrecovery objects or clustered EEG arousals). If these are identifiedthen the region of the cluster occurrences is compared to the identifiedhypopnea region derived from the conventional method. If this region isas recognized as hypopneas then the pre-selected pressure for a givenincrement in titration is further incremented by 1-2 cm so thatconventional titration occurs at higher-pressure levels and the processis repeated until all clusters are eliminated. (If EEG arousals worsenwith this increase then the increment can be withdrawn). If on the otherhand the algorithm did not recognize this region as a hypopnea thethreshold criteria for a hypopnea is reduced until the clusters areeliminated (in some cases require a baseline fixed pressure of 2-3 ormore cm.). FIG. 17 shows a CPAII auto-titration system which uses themulti-signal object dataset during one or more auto adjusting learningnights to customizes at least one of the treatment response to a giventriggering threshold or the triggering threshold to a given treatmentresponse. The application of a learning night can prevent inappropriateor unnecessary adjustments and can provide important information abouttreatment response while assuring that the basic algorithm itself iscustomized to the specific patient upon which it is applied. This isparticularly useful in the hospital using hospital-based monitors wherethe monitor is coupled with the processor of the CPAP unit for thelearning nights while in the hospital. Alternatively learning nights canbe provided at home by connecting a primary processor for processingmultiple signals with the processor of the CPAP unit for a few nights tooptimize the algorithm for later use. In the hospital all of thecomponents can be used to assure optimal titration, using the an objectsbased cluster analysis of simultaneous tracing of chest wall impedanceand oximetry the titration can be adjusted to assure mitigation of allclusters, alternatively, if they are not mitigated by the titration thenthe nurse is warned that these clusters are refractory and to considercentral apnea (particularly if the impedance movements during the apneasare equivocal or low). If for example, the patient's oxygen saturationfalls (after adjusting for the delay) in response to an increase inpressure, the pressure can be withdrawn and the nurse warned thatdesaturation unresponsive to auto titration is occurring or bilevelventilation can be automatically initiated. The self-customizing autotitration system can include a pressure delivery unit capable of autoadjusting either CPAP or BIPAP such that such a desaturation in responseto CPAP can trigger the automatic application of BIPAP.

As discussed, according to the present invention, clusters of hypopneascan generally be reliably recognized utilizing with only a singleparameter. However, when significant signal noise or reduced gain ispresent, the objects based system can combine matched clusters within atime series of multi-signal objects in the presence of sub optimalsignals by providing a scoring system for sequential objects. FIGS. 13,14, and 15 show schematics of the basic cluster matching in situationswherein sub optimal signals may be present. The multi-signal objectsdefining the matched clusters of paired timed datasets of airflow andoximetry include a matched sequence of negative cycle objects in theairflow signal and corresponding negative cycle object in the oximetrysignal. Each cycle object is defined by a set of coupled rise and fallobjects meeting criteria and occurring within a predetermined intervalof each other (as discussed previously). The occurrence of a cycleobject in either dataset meeting all criteria is given a score of 1. Thecycles are counted in sequence for each multi-signal cluster object. Forthe purpose of illustration, according to the present invention, theoccurrence of a score of 3 in any one signal (meaning that a sequence of3 cycles meeting criteria have occurred within a specified interval)provides sufficient evidence to identify a cluster object. When twosimultaneous signals are processed, a total score of 4, derived fromadding the number of cycles meeting criteria in each signal, issufficient to indicate the presence of a cluster object. In this mannerthe cluster is continued by a sequential unbroken count greater than 3with one signal, or greater than 4 with two signals. Once the presenceof a cluster object has been established along the time series, at anypoint along the cluster object the sequential count along one signal canbe converted to a continuation of the sequential count along anothersignal allowing the cluster object to continue unbroken. The failure ofthe occurrence of a cycle meeting criteria within either signal within aspecified interval (for example about 90-120 seconds, although otherintervals may be used) breaks the cluster object. A new cluster objectis again identified if the count again reaches the thresholds as notedabove. It can be seen that this scoring method takes into account thefact that artifact often affects one signal and not another. Thereforeif either signal alone provides a sufficient score, the presence of acluster object is established. In addition, the effect of brief episodesof artifact affecting both signals is reduced by this scoring method. Inthis way, artifact, unless prolonged, may cause the cluster object to bebroken but as soon as the artifact has reduced sufficiently in any oneor more signals the process of scoring for a new cluster object willrestart.

Another CPAP auto titration system according to the present invention anautomatic CPAP titration unit includes a processor and at least onesensor for sensing a signal transmitted through the nose such as apressure signal indicative of airflow, sound and/or impedance as isknown in the art. An oximeter, which can be detachable or integratedinto the CPAP unit, is connected Keith the processor. The processordetects by poventilation, using output from both the flow sensor and theoximeter, when the oximeter is attached, and in the embodiment with adetachable oximeter, when the oximeter is not attached the processordetects hypoventilation using the flow sensor without oximetry.

According to another aspect of the present invention, the multi-signalobject time series can be used for identifying pathophysiologicdivergence. Pathophysiologic divergence can be defined at thefundamental, composite, or complex level. An example of divergence atthe fundamental level is provided by the relationship between an airflowrise object (inspiration) and a fall object (expiration). Along a timeseries of matched expiration and inspiration objects, the occurrence ofa marked increase in amplitude of inspiration is commonly associatedwith an increase in the ratio of the absolute value of inspiration slopeto the absolute value of the slope of exhalation. Should this valueincrease, this provides evidence suggesting pathophysiologic divergence.Alternatively, in a preferred embodiment of the present invention, theevaluation time period can be much longer. In one embodiment, theobjects defining the data set of the first time interval is compared tothe objects defining the data set of the second corresponding timeinterval. This comparison is performed in a similar manner to theaforementioned comparison of corresponding cluster objects noted supra.The specific parameters, which are compared, are parameters having knownpredictable physiologic linkages wherein a change of first physiologicparameter is known to induce a relatively predictable change in a secondphysiologic parameter. The second parameter is, therefore, aphysiologically subordinate of the first parameter. As shown in FIG. 11,the first parameter can be a measure indicative of the timed volume ofventilation and the second parameter can be the timed arterial oxygensaturation. Here, as shown in FIG. 11, a progressive rise in minuteventilation is expected to produce rise in oxygen saturation. Thealveolar gas equation, the volume of dead space ventilation and theoxyhemoglobin disassociation curve predict the rise in oxygen saturationby known equations. However, according to one aspect of the presentinvention, it is not necessary to know the absolute predicted value ofoxygen saturation rise for a given change in minute ventilation butrather the processor identifies and provides an output indicatingwhether or not an expected direction of change in the subordinate oneparameter occurs in association with a given direction of change in theprimary parameter. For example, with respect to arterial oxygensaturation and ventilation, it is the preferred purpose of oneembodiment of the present invention to determine whether or not anexpected direction and/or slope of change of oxygen saturation occur inassociation with a given direction and/or slope change in minuteventilation. The time course of the rise in ventilation of FIG. 11 isshort however, as the time period lengthens the relationship isstrengthened by the greater number of corresponding measurements and thegreater measurement time. When minute ventilation slopes or trendsupward over a sustained period, after the anticipated delay there wouldbe an expected moderate upward change in oxygen saturation if thesaturation is not already in the high range of 97-100%. If, on the otherhand, if the oxygen saturation is falling during this period, this wouldsuggest that the patient is experiencing a divergent pathophysiologicresponse which may warrant further investigation. Automatic recognitionof falling or unchanged oxygen saturation in association with a risingminute ventilation can provide earlier warning of disease than isprovided by the simple non-integrated monitoring and analysis of thesetwo wave forms.

One of the advantages provided by the present invention is that it isnot necessary to be exact with respect to the measurement of minuteventilation. Minute ventilation can be trended by conventional methods,without an absolute determination of the liters per minute for example,by plotting a measure of the amplitude and frequency of a nasal oralthermister or by the application of impedance electrodes on the chest,thereby monitoring the amplitude and frequency of tidal chest movement.Alternatively conventional impedance or stretch sensitive belts aroundthe chest and abdomen or other measures of chest stall and/or abdominalmovement can be used to monitor tidal ventilation and then this can bemultiplied times the tidal rate of breathing to provide a general indexof the magnitude of the minute ventilation. In the preferred embodiment,the minute ventilation are trended on a time data set over a five tothirty minute intervals along with the oxygen saturation.

In one presently preferred embodiment, the monitoring system foridentification of pathophysiologic divergence of timed output is shownin FIG. 8. As discussed previously, the monitor includes amicroprocessor 5, the first sensor 20, a second sensor 25, and an outputdevice 30 which can be a display or a printer, but preferably wouldinclude both. The processor 5 is programmed to generate a first timedwaveform of the first parameter, derived from the first sensor 20, and asecond timed waveform of second parameter, derived from the secondsensor 25. Using the multi-signal processing system, describedpreviously, the processor 5 compares the objects of the first timedoutput to the objects of the second timed output to identify unexpecteddivergence of the shape of the first timed output to the shape of thesecond timed output and particularly to recognize a divergence indirectional relationship or polarity of one timed output of oneparameter in relationship to another timed output of another relatedparameter. In one preferred embodiment, this divergence comprises a fallin the slope of the oxygen saturation (for example, as defined by therecognition of a “decline object”, as discussed previously) inrelationship to a rise (referred to as a “rise object”) in the slope ofthe corresponding minute ventilation. In another example, the processorintegrates three signals to identify divergence. The processoridentifies the relationship of other signals such as heart rate orR-to-R interval or a measure of the pulse magnitude (as the amplitude,slope of the upstroke, or area under the curve of the plethesmographicpulse). In particular, a rise object in minute ventilation may beidentified in association with a decline object in oxygen saturation anda decline object in heart rate or pulse amplitude. These outputs can beplotted on a display 30 for further interpretation by a physician withthe point of pathophysiologic divergence of one parameter inrelationship to another parameter identified by a textural or othermarker.

The identification of pathophysiologic divergence can result insignificant false alarms if applied to the short time intervals used forrise and decline objects which are used for detection of cluster objects(and also the short averaging intervals for this purpose). Inparticular, if the identification of divergence is applied for shortintervals, such as 1 to 2 minutes, a significant number of falseepisodes of divergence will be identified. One purpose of the presentinvention is to provide clear evidence of a trend in one measuredparameter in relationship to a trend of another measured parameter sothat the strong definitive evidence that divergence has indeed occurred.According to the present invention, this can be enhanced by theevaluation of the prolonged general shape or polarity of the signal sothat it is considered preferable to identify divergence over segments offive to thirty minutes. The averaging of many composite objects toidentify a rise object at the complex object level helps mitigate suchfalse alarms. For this reason, the expected time course of a divergencetype must be matched with the resolution (or averaging times) of theobjects compared.

According to one aspect of the invention, to enhance the reliability ofthe analysis of the timed data set, the averaging interval, for thispurpose, can be adjusted to avoid excessive triggering of theintermittent monitoring device. In one preferred embodiment, theaveraging interval is increased to between thirty and ninety seconds oronly the analysis of complex objects can be specified. Alternativemethods may be used to identify a rise and fall objects such as theapplication of line of best-fit formulas, as previously discussed.Elimination of outlier data points to define larger composite objectscan also be applied as also previously discussed or by other methods. Inthis way the identification of a trend change, which evolves over aperiod of five to fifteen minutes, can be readily identified. Theidentification of divergence can produce a textual output, which can bemaintained for a finite period until the secondary parameter corrects ora threshold period of time has elapsed. For example, if a rise in minuteventilation is identified over a predetermined interval period (such asabout ten minutes) to define a rise object and a fall in oxygensaturation is identified over a corresponding period to define a fallobject, the processor identifies the presence of divergence and canproduce a textual output which can be provided on the bedside display orcentral processing display. This textual output can be maintained for afinite period, for example, one to two hours, unless the oxygensaturation returns to near its previous value, at which time the textualoutput ma % he withdrawn from the display.

In this flay the presence of pathophysiologic divergence is readilyidentified, however, since divergence is defined by divergent rise andfall objects of corresponding physiologically linked parameters, itsduration is necessarily limited since these slopes can not continue todiverge indefinitely. It is important to carry forward theidentification of prior divergence in the patient's display for at leasta limited period of time so that the nurse can be aware that this eventhas occurred. For example, a “fall object” identified in the secondary,signal such as a fall in oxygen saturation from 95% to 90% over a periodof ten minutes occurring in association with a rise object in theprimary signal, such as, for example, a doubling of the amplitude- ofthe airflow or chest wall impedance deflection over a period oftenminutes can produce an identification of pathophysiologic divergencewhich can be linked to the outputted saturation so that the displayshows a saturation of 90% providing an associated textual statement“divergence-TIME”. This identification of divergence can, over a periodof time, be withdrawn from the display or it can be immediatelywithdrawn if the oxygen saturation corrects back close to 95%.

As discussed previously and as also illustrated in FIG. 8, in anotherpreferred embodiment of the present invention, a change in theconfiguration of the multi-signal time series can be used to trigger theaddition of one or more additional signals to the multi-signal timeseries, such as a non-invasive blood pressure, to identify whether ornot pathophysiologic divergence is occurring with respect to the new,less frequently sampled signal. For example, the trending rise in heartrate should not be generally associated with a fall in blood pressure.If, for example over a period of 5 to 20 minutes, a significant rise inheart rate (as for example a 25% rise and at least 15 beats per minute)is identified by the processor, according to the present invention, themonitor can automatically trigger the controller of a non-invasive bloodpressure monitor to cause the measurement of blood pressure to beimmediately taken. The output of the non-invasive blood pressure monitoris then compared by the processor to the previous value which wasrecorded from the blood pressure monitor and, if a significant fall inblood pressure (such as a fall in systolic of 15% and more) isidentified in association with the identified rise in heart rate whichtriggered the test, a textual warning can be provided indicating thatthe patient is experiencing pathophysiologic divergence with respect toheart rate and blood pressure so that early action can be taken beforeeither of these values reach life-threatening levels. According toanother aspect of the invention a timed dataset of the pulse rate isanalyzed, if a significant change (for example a 30-50% increase in therate or a 30-50% decrease in the interval or a 50-75% increase in thevariability of the rate), then the blood pressure monitor can betriggered to determine if a significant change in blood pressure hasoccurred in relation to the change in pulse rate or the R to R interval.

This can be threshold adjusted. For instance, a significant rise inheart rate of 50% if lasting for a period of two and a half minutes canbe used to trigger the intermittent monitor, whereas a more modest risein heart rate of, for example, 25% may require a period of five or moreminutes before the intermittent monitor is triggered.

In another embodiment, also represented in FIG. 8, identification by thebedside processor 5 of a sustained fall in oxygen saturation can be usedto trigger an ex-vivo monitor 40 to automatically measure the arterialblood gas parameters. Alternatively, a significant rise in respiratoryrate (for example, a 100% increase in respiratory rate for five minutes)can suffice as a trigger to automatically evaluate either the bloodpressure or an ex-vivo monitor of arterial blood gasses.

There are vulnerabilities of certain qualitative indexes of minuteventilation in relationship to divergence, which the present inventionserves to overcome to enhance the clinical applicability of the output.For example, a rise in the signal from chest wall impedance can beassociated with a change in body position. Furthermore, a change in bodyposition could result in a fall of oxygen saturation due to alterationin the level of ventilation, particularly in obese patients, suchalterations can be associated with an alteration in the ventilationperfusion matching in patients with regional lung disease. Therefore, achange in body position could produce a false physiologic divergence ofthe signals when the multi-signal time series includes chest wallimpedance and oximetry. For this reason, according to the presentinvention, additional time series components may be required, such asoutputted by a position sensor, or alternatively, if this information isnot available, a more significant fall in one parameter may be requiredin association Keith a more significant divergent rise in another. Forexample, a significant fall in oxygen saturation of, for example, 4-5%in association with a doubling of the product of the amplitude andfrequency of the impedance monitor would provide strong evidence thatthis patient is experiencing significant pathophysiologic divergence andwould be an indication for a textual output indicating thatpathophysiologic divergence has occurred. The thresholds for definingdivergence, according to the present invention, may be selectable by thephysician or nurse. When the time series output of a position monitor isincorporated into the system with a significant change in one or moreparameter, which is temporarily related to a position change, itprovides important additional information.

According to the present invention, the magnitude of pathophysiologicdivergence can be provided on the central display 38 or bedside display30. In some cases, as discussed previously, a mild degree ofpathophysiologic divergence may not represent a significant change andthe nurse may want to see, rather, an index of the degree ofpathophysiologic divergence. A bar graph or other variable indicator,which can be readily observed such as the monitoring cubes of 6 a-6 e,can provide this. In one embodiment the monitoring cube can beselectively time lapsed to observe the previous relational changesbetween parameters, or alternatively the animated object can be rotatedand scaled to visually enhance the represented timed relationships andpoints of divergence.

In one embodiment, the multi-signal time series output is placed into aformat particularly useful for reviewing events preceding an arrest orfor physician or nurse education. In this format the output controls ananimation of multiple objects which, instead of being parts of a hexagonor cube are shaped into an animated schematic of the as the physiologicsystem being monitored. The animation moves over time and in response tothe signals and one preferred embodiment the type of signals (or thereliability of such signals) determines which components of theschematic are “turned on” and visible. One example includes amulti-signal object defined by outputs of airflow, thoracic impedance,oximetry, and blood pressure rendering set of a connected set animationobjects for the lungs, upper airway, lower airway, heart, and bloodvessels which can be animated as;

-   -   Each inspiration causing an animated enlargement of the lungs        tracking the inspiration slope,    -   Each expiration causing an animated reduction in size of the        lungs tracking the expiration slope,    -   Each animated systolic beat of the heart tracks the QRS or        upstroke of the oximetry output,    -   The color of the blood in the arteries and left heart tracks the        oxygen saturation,    -   The diameter of the lower airway (a narrowing diameter can be        highlighted in red) tracks the determination of obstruction by        the slope ratio in situations of hyperventilation (as discussed        previously),    -   The patency of the upper airway (a narrowing or closure can be        highlighted in red) tracks the determination of upper airway        obstruction (as discussed previously).    -   The magnitude of an animated pressure gauge tracks the blood        pressure.

This provides “physiologic animation” which can be monitored inreal-time but will generally be derived and reviewed from the storedmulti-signal objects at variable time scales. This is another example ofan embodiment of the present invention providing a quickly, easilyunderstood and dynamic animated output of a highly complex, interactivetime series derived form a patient. The animation can be reviewed at anincreased time lapsed to speed through evolution of a given patientsoutputs or can be slowed or stopped to see the actual global physiologicstate at the point of arrhythmia onset.

In another example of a more simple signal relationship indicator, apatient with a drop in oxygen saturation of 4% and a doubling of theproduct of the frequency and amplitude of the chest wall impedance tidalvariation may have a single bar presented on the monitor, whereas, apatient with a 6% drop wherein the product of the impedance amplitudeand frequency has tripled may have a double bar, and so on. This allowsreduction in the occurrence of false alarms by providing a bar indicatorof the degree of divergence which has occurred. A similar indicator canbe provided for clustering, indicative of the severity of airway orventilation instability. Since very mild clustering may simply representthe effect of moderate sedation, and not, therefore, represent a causefor great concern (although it is important to recognize that it ispresent). Such a clustering could be identified with a single bar,whereas more severe clustering would generate a larger warning and, itvery severe, an auditory alarm. When the clustering becomes more severeand demonstrates greater levels of desaturation and/or shorter recoveryintervals the bar can be doubled.

In another embodiment, which is particularly useful for neonates, thetime series of multi-signal objects is derived entirely from a pulseoximeter. Each object level for each signal and further a multi-signalobject time series of the oxygen saturation and pulse (as for examplecan be calculated below) is derived. This particular multi-signal timeseries has specific utility for severity indexing of apnea ofprematurity. The reason for this is that the diving reflex in neonatesand infants is very strong and causes significant, cumulativebradycardia having a progressive down slope upon the cessation. Inaddition, the apnea is associated with significant hypoxemia, which alsocauses a rapid down slope due to low oxygen storage of these tinyinfants. Even a few seconds of prolongation of apnea causes profoundbradycardia because the fall in heart rate like that of the oxygensaturation does not have a reliable or nadir but rather falls throughoutthe apnea. These episodes of bradycardia cluster in a manner almostidentical to that of the oxygen saturation, the pulse in the neonatebeing a direct subordinate to respiration.

In neonates, oxygen delivery to the brain is dependent both upon thearterial oxygen saturation and the cardiac output. Since bradycardia isassociated with a significant fall in cardiac output, oxygen delivery tothe neonatal brain is reduced both by the bradycardia and the fall inoxygen saturation. It is critical to have time series measure, whichrelates to cumulative oxygen delivery (or the deficit thereof) both as afunction of pulse and oxygen saturation. Although many indices can bederived within the scope of the present invention, the presentlypreferred index is given as the “Saturation Pulse”. Although manscalculations of this index are possible in one presently preferredembodiment the index is calculated as:SP=R(SO2−25)Where:

-   -   SP is the saturation pulse in “% beats/sec.”.    -   R is the instantaneous heart rate in beats per second, and    -   SO2 is the oxygen saturation of arterial blood in %.

The saturation-pulse is directly related to the brain oxygen delivery.The SpO₂−25 is chosen because 25% approaches the limit of extractableoxygen in the neonatal brain. The index is preferably counted for eachconsecutive acquisition of saturation and pulse to produce a continoustime series (which is an integral part of a multi-signal time series ofoxygen saturation and pulse). This index can be calculated for over thetime interval of each apnea and each cluster to derive an apnea orcluster index of saturation-pulse during apnea and recovery in a manneranalogous to that described in U.S. Pat. No. 6,223,064. This provides anenhanced tool for severity indexing of apnea of prematurity in infants.Both the duration and the absolute value of any decrement insaturation-pulse are relevant. If preferred the average maximuminstantaneous, and cumulative deficit of the pulse saturation index canbe calculated for each cluster (as by comparing to predicted normal orautomatically calculated, non apnea related baseline values for a givenpatient).

In this way, according to the present invention, a general estimate ofoxygen delivery over time to the infants brain is provided using anon-invasive pulse oximeter through the calculation of both oxygensaturation and pulse over an extended time series deriving a cumulativedeficit specifically within clusters of apneas to determine index of thetotal extent of global decrease in oxygen delivery to the brain duringapnea clusters. The deficit can be calculated in relation to either thebaseline saturation and pulse rate or predicted normals.

The processor can provide an output indicative of the pulse saturationindex, which can include an alarm, or the processor can trigger anautomatic stimulation mechanism to the neonate, which will arouse theneonate thereby aborting the apnea cluster. Stimulation can include atactile stimulator such as a vibratory stimulator or other device, whichpreferably provides painless stimulation to the infant, thereby causingthe infant to arouse and abort the apnea cluster.

In another embodiment of the system, the recognition of a particularconfiguration and/or order of objects can trigger the collection ofadditional data points of another parameter so that these new datapoints can be added to and compared with the original time series torecognize or confirm an evolving pathophysiologic process. Oneapplication of this type of system is shown in FIG. 8 and illustratedfurther in FIG. 18. The time series of pulse, oxygen saturation, and/orcardiac rhythm can be used to trigger an automatic evaluation of bloodpressure by a non-invasive blood pressure device. The bedside processorA, upon recognition of tachycardia by evaluation of the pulse or EKGtracing, automatically causes the controller of the secondary monitoringdevice 40 to initiate testing. The nurse is then immediately notifiednot only of the occurrence, but also is automatically provided with anindication of the hemodynamic significance of this arrhythmia. In thissituation, for example, the occurrence of an arrhythmia lasting for atleast twenty seconds can trigger the automatic comparison of the mostrecent blood pressure antecedent the arrhythmia and the subsequent bloodpressure, which occurred after the initiation of the arrhythmia. Theprocessor identifies the time of the initial blood pressure, whichoccurred prior to the point of onset of the arrhythmia, and the time ofevaluation of the blood pressure after the onset of the arrhythmia andthese are all provided in a textural output so that the nurse canimmediately recognize the hemodynamic significance of the arrhythmia.Upon the development of a pulse less arrhythmia a printed output istriggered which provides a summary of the parameter values over a range(such as the 5-20 minutes) prior to the event as well as at the momentof the event. These are provided in a graphical format to be immediatelyavailable to the nurse and physician at the bedside during theresuscitation efforts so that the physician is immediately aware ifhyperventilation, or oxygen desaturation preceded the arrhythmia (whichcan mean that alternative therapy is indicated

According to another aspect of the invention, if the patient does nothave a non-invasive blood pressure cuff monitor attached, but rather hasonly a pulse oximeter or an impedance based non-invasive cardiac outputmonitor and an electrocardiogram attached, then the multi-level timeseries plethsmographic pulse objects can be used to help determine thehemodynamic significance of a given change in heart rate or thedevelopment of an arrhythmia. In this manner, the identification ofsignificant change in the area under the curve associated with asignificant rise in heart rate or the development of an arrhythmia cancomprises a multi-signal object indicative of potential hemodynamicinstability.

If the multi-signal object includes a new time series of wide QRScomplexes of this occurrence is compared to the area under theplethesmographic pulse to determine the presence of “pulseless” or “nearpulseless” tachycardia. It is critical to identify early pulselesstachycardia (particularly ventricular tachycardia) since cardioversionof pulseless tachycardia may be more effective than the cardioversion ofventricular fibrillation. On the other hand, ventricular tachycardiaassociated with an effective pulse, in some situations, may not requirecardioversion and may be treated medically. Timing in both situations iscritical since myocardial lactic acidosis and irreversible intracellularchanges rapidly develop and this reduces effective cardioversion. It is,therefore, very important to immediately recognize whether or not thesignificant precipitous increase in heart rate is associated with aneffective pulse. The plethesmographic tracing of the oximeter canprovide indication of the presence or absence of an effective pulse.However, displacement of the oximeter from the proper position on thedigit can also result in loss of the plethesmographic tracing. For thisreason, according to the present invention, the exact time in which thewide QRS complex time series developed is identified and related to thetime of the loss of the plethesmographic pulse. If the plethesmographicpulse is lost immediately upon occurrence of a sudden increase of heartrate (provided that the signal does not indicate displacement), this isnearly definitive evidence that this is a pulseless rhythm and requirescardioversion. The oxygen saturation and thoracic impedance portion ofthe multi-signal object is also considered relevant for theidentification of the cause of arrhythmia. At this moment an automaticexternal cardioversion device can be triggered to convert the pulselessrhythm. In an alternative embodiment, as also shown in FIG. 18, a bloodpressure monitor which can be a non-invasive blood pressure monitorintegrated with the automatic defibrillator can be provided. Upon therecognition of a precipitous increase in heart rate, this event cantrigger automatic non-invasive blood pressure evaluation. If thenon-invasive blood pressure evaluation identifies the absence ofsignificant blood pressure and pulse and this is confirmed by theabsence of a plethesmographic pulse, then the processor can signal thecontroller of the automatic cardio version unit to apply and electricalshock to the patient based on these findings. It can be seen thatmultiple levels of discretionary analysis can be applied. The firstbeing the identification of a precipitous development of a wide complextachyarrhythmia in association with simultaneous loss ofplethesmographilc pulse which can trigger an automatic synchronizedexternal cardio version before the patient develops ventricularfibrillation. The second requires confirmation by another secondarymeasurement such as loss of blood pressure, the lack of the anticipatedcycle of chest impedance variation associated with normal cardiac outputas with a continuous cardiac output monitor, or other indication.

It can be seen that even without the EKG time series component object ananalysis of the multi-signal can be applied to compare the area underthe curve of the plethesmographic pulse tracing generated by a pulseoximeter to a plot of peak-to-peak interval of the pulse tracings. Thesudden decrease in the peak-to-peak interval or increase in pulse ratein association with a sudden decrease in the plethesmographic area isstrong evidence that the patient has experienced a hemodynamicallysignificant cardiac arrhythmia. In the alternative, a moderate andslowly trending upward increase in heart rate in association pith amoderate and slowly trending downward plot of the area of theplethesmographic pulse would be consistent with intervascular volumedepletion, or ineffective cardiac output resulting from significantsympathetic stimulation which is reducing the perfusion of theextremities as with as congestive heart failure. During such a slowevolution it would also be anticipated that the frequency of tidalrespirations would increase.

In one preferred embodiment, a motion detection algorithm can also beapplied. The data set generated by the motion detection comprises a timeseries component of the multi-signal object. If significant motion isidentified at the time of the occurrence of both the tachyarrythmia andthe loss of the plethesmographic pulse and the motion continues to bepresent then automatic external cardio version would not go forward andthe device would simply provide a loud auditory) and prominent visualalarm. The reason for this adjustment is that motion can in rare casessimulate the presence of a tachyarrhythmia and, further, such motion canresult in loss of a detectable plethesmographic pulse. Rhythmic tappingof the chest wall lead of an electrocardiogram with the same finger towhich the probe of the pulse oximeter is attached, theoretically, couldsimulate the occurrence of pulseless ventricular tachycardia. Inaddition, the development of a chronic seizure, which results insignificant chest wall artifact, as well as rhythmic motion of theextremities could also simulate the development of pulselesstachycardia. For these reasons, according to the present invention, thepresence of significant motion can be used to prevent the processor fromsignaling the controller of the automatic external cardio version devicefrom shocking the patient.

According to another aspect of the present invention, a change in one ormore time series components of the multi-signal object can be used tochange the processing algorithm of a time series component of themulti-signal object. In an example, the recognition of airwayinstability is enhanced by improved fidelity of the timed waveform (aswith pulse oximetry). FIG. 16 shows one preferred method, according tothe present invention, of improving the general fidelity of the entiretimed waveform of SpO₂ for enhanced pattern cluster recognition in anenvironment where the patient, at times, has motion and, at other times,does not. It is optimal, for example, in monitoring oximetry for theprobe to be placed on a portion of the patient, which is not associatedwith motion. However, in most cases, this is unrealistic and motion iscommonly associated with routine clinical oximetry monitoring. It iswell known that motion results in a fall in the saturation value, whichis generated by the oximeter. Multiple theories for the cause of thefall have been promulgated. Several corporations, including Masimo, andNellcor had developed algorithms, which can be used to mitigate theeffect of motion on the accuracy of the output. However, such algorithmscan include a significant amount of signal averaging, generally fourseconds or more. This can result in significant smoothing of thewaveform and reduces the fidelity of the waveform. Furthermore,it-attenuates patterns of minor desaturations, which can be indicativeof airway instability, and clusters of hypopneas associated withvariations in airway resistance. As discussed in the aforementionedpatents and patent application, even minor desaturations when occurringin clusters can be strong evidence for airway or ventilation instabilityand it is important to recognize such desaturations. Unfortunately,averaging intervals, especially those exceeding four seconds or more canresult in attenuation of these desaturations and, therefore, hide theseclusters so that the airway instability may not be recognized. However,motion itself results in artifact, which can simulate desaturations.Although such artifact is not expected to occur in typical clusterpattern, the presence of motion artifacts significantly reduces thevalue of the signal as an index of oxygen saturation and airwayinstability. The present invention thereby provides for more optimalcontinuous fidelity of the waveform through both motion and non-motionstates. As illustrated in FIG. 16, when the motion time series outputsuggests that substantial motion is not present, such as deep sleep orsedation, wherein the extremity is not moving, long averaging smoothingalgorithms or motion mitigation algorithms are not applied to the oxygensaturation and plethesmographic pulse time series. In the alternative,if the series indicates motion then these motion mitigation algorithmsare applied. The variable application of averaging based onidentification of the absence or presence of motion provides optimalfidelity of the waveform for monitoring airway instability.

Those skilled in the art will recognize that, the information providedfrom the data and analysis generated from the above-described system canform the basis for other hardware and/or software systems and has widepotential utility. Devices and/or software can provide input to or actas a consumer of the physiologic signal processing system of the presentinvention's data and analysis.

The following are examples of presently preferred ways that the presentphysiologic signal processing system can interact with other hardware orsoftware systems:

-   -   1. Software systems can produce data in the form of a waveform        that can be consumed by the physiologic signal processing        system.    -   2. Embedded systems in hardware devices can produce a real-time        stream of data to be consumed by the physiologic signal        processing system.    -   3. Software systems can access the physiologic signal processing        system representations of populations of patients for        statistical analysis.    -   4. Software systems can access the physiologic signal processing        system for conditions requiring hardware responses (e.g.        increased pressure in a CPAP device), signal the necessary        adjustment and then analyze the resulting physiological response        through continuous reading of the physiologic signal processing        system data and analysis.

It is anticipated that the physiologic signal processing system will beused in these and many other ways. To facilitate this anticipatedextension through related hardware and software systems the presentsystem will provide an application program interface (API). This API canbe provided through extendable source code objects, programmablecomponents and/or a set of services. Access can be tightly coupledthrough software language mechanisms (e.g. a set of C++ modules or Javaclasses) or proprietary operating system protocols (e.g. Microsoft'sDCOM, OMG's CORBA or the Sun Java Platform) or can be loosely coupledthrough industry standard non-proprietary protocols that providereal-time discovery and invocation (e.g. SOAP [Simple Object AccessProtocol] or WSDL [Web Service Definition Language]).

In the preferred embodiment the physiologic signal processing systemwith the API as defined becomes a set of programmable objects providinga feature-rich development and operating environment for future softwarecreation and hardware integration.

Although the presently preferred embodiments have been described, whichrelate to the processing of physiologic signals, it is also critical torecognize the present streaming parallel objects based data organizationand processing method can be used to order and analyze a wide range ofdynamic patterns of interactions across a wide range of correspondingsignals and data sets in many environments. The invention is especiallyapplicable to the monitoring of the variations or changes to a physicalsystem, biologic system, or machine subjected to a specific process orgroup of processes over a specific time interval.

The invention provides a new general platform for the organization andanalysis of a very wide range of datasets during hospitalization or asurgical procedure. For example, in addition to the time series of themonitored signals parameters, which may be sampled at a wide range (forexample between about 500 hertz and 0.01 hertz), previously noted, thecylindrical data matrix can include a plurality of time series oflaboratory data, which may be sampled on a daily basis or only onceduring the hospitalization. These data points or time series are storedas objects and can be included in the analysis. These objects caninclude, for example the results of an echocardiogram wherein a timedvalue ejection fraction of the left ventricle is provided as an objectin the matrix for comparison with other relationships. In application,the presence of a low ejection fraction object along the matrix with aparticular dynamic cyclic variation relationship between airflow andoxygen saturation time series can, for example, provide strong evidenceof periodic breathing secondary to congestive heart failure and thisidentified relationship can be provided for the healthcare worker in atextual output. In another example the medications are included in datamatrix. For example in a patient receiving digoxin and furosemide (adiuretic) the daily serum potassium time series is compared to a timeseries indicative of the number and severity of ventricular arrhythmiassuch as premature ventricular contractions. A fall in the slope of thepotassium time series in association with a rise in slope of such anarrhythmia indication time series could for example produce an outputsuch as “increased PVCs—possibly secondary to falling potassium,consider checking digoxin level”. In another example a first time seriesof the total carbon dioxide level and a second time series of the aniongap can be included in the general streaming object matrix and comparedto the time series of airflow. If a rise in the slope or absolute valuesof the airflow is identified with a fall in the slope or absolute valuealong the total carbon-dioxide time series and a rise the slope orabsolute values alone the anion gap time series, the processor canprovide an automatic identification that the airflow is rising and thatthe cause of a rise in airflow may be secondary to the development of apotentially life threatening acidosis, providing an output such as“hyperventilation—possibly due to evolving anion gap acidosis”. Inanother example, the daily weight or net fluid balance is included withthe total carbon dioxide and anion gap in the cylindrical data matrix.The identification of a fall in slope of airflow or absolute value alongthe associated with a fall in slope of the oxygen saturation, and a fallin slope of the fluid balance and weight can generated a output such as“possible hypoventilation-consider contraction alkalosis”.

Alternatively with a matrix made up of the same parameters, a rise inthe slope or absolute values of the airflow time series and a rise inthe pulse time series may be recognized in comparison with a fall in thetime series of the total carbon dioxide, a flat slope of the time seriesof the anion gap, and a rise in the slope or absolute values of thefluid balance time series, confirmed by a trending rise in slope of theweight time series, and a notification can be provided as“hyperventilation—potentially secondary to expansion acidosis orcongestive heart failure”. In one preferred embodiment the cylindricaldata matrix becomes the platform upon which substantially all relevantdata derived during a hospitalization is stored and processed fordiscretionary and automatic comparison. Initial input values, which canbe historical input, can also be included to set the initial state ofthe data matrix. For example, if the patient is known to have a historycongestive heart failure, and that is inputted as an initial data pointat the start of the matrix and that particular conformation in theinitial matrix is considered in the analysis. The data matrix provides apowerful tool to compare the onset of dynamic changes in parameters withany external force acting on the organism whether this force ispharmacological, a procedure, related to fluid balance, or even simpletransportation to other departments for testing. In one preferredembodiment, as shown in FIG. 1 b, a time series of action applied to thepatient is included called an “exogenous action time series”. This timeseries includes a set of streaming objects indicating the actions beingapplied to the patient throughout the hospitalization. In this example,within the exogenous action time series a time series componentindicative of dynamic occurrence of a particular invasive procedure,such as the performance of bronchoscopy, is included. This“bronchoscopic procedure object” may, for example, comprise a timeseries component along the exogenous action time series of 15 minuteswithin the total matrix derived from the hospitalization. The dynamicrelationships of the parameters along the matrix are compared with theonset of the procedure (which comprising an object onset), dynamicpatterns of interaction evolving subsequent to the onset of theprocedure can be identified and the temporal relationship to theprocedure object identified and outputted in a similar manner as hasbeen described above for other objects. The dynamic patterns ofinteraction can be interpreted with consideration of the type ofprocedure applied. For example, after a 15 minute time series associatedwith a bronchoscopic procedure, the occurrence of a progressive increasein slope of the airflow time series associated with a significantdecrease in the slope of the inspiration to expiration slope ratio timeseries suggests the development of bronchospasm secondary to thebronchoscopy and can initiate an output such as “hyperventilationpost-bronchoscopy with decreased I:E—consider bronchoscopy,”. A largersurgical procedure comprises a longer cylindrical data matrix and thiscan comprise a perioperative matrix, which can include the portion oftime beginning with the administration of the first preoperativemedication so that dynamic patterns of interaction are compared withconsideration of the perioperative period as a global time series objectwithin the matrix, with the preoperative period, the operative period,and the post operative period representing time-series segment of thematrix within the total hospital matrix. Using this objects basedrelational approach a “dynamic pattern of” interaction occurring withinthis procedure related data stream or subsequent to it can be easilyrecognized and temporally correlated with the procedure so that thedynamic relationships between a procedure and plurality of monitoredtime series outputs and/or laboratory data are stored, analyzed, andoutputted. In another example, the continuous or intermittent infusionof a pharmaceutical such as a sedative, narcotic, or inotropic drugcomprises a time series which has as one of its timed characteristicsthe dose administered. This new time series is added to the cylindricalmatrix and the dynamic relationships between monitored signals andlaboratory data is compared. For example after the initiation ofDobutamine (an inotropic drug) the occurrence of a rising slope of pulserate or a risings slope of premature ventricular contraction frequency,or the occurrence of an object of non sustained ventricular tachycardia,can be recognized in relation to onset the time series of medicationinfusion or a particular rise in the slope or absolute value of the ofthe dose of this medication. In another example the occurrence of adynamic clustering of apneas such as those presented in FIG. 10, 11, and5 c in relation to a rise in slope, or a particular absolute value, ofthe time series of the sedative infusion can he identified and the pumpcan be automatically locked out to prevent further infusion and anoutput such as “Caution—pattern suggestive of mild upper airwayinstability at dose of 1 mg Versed.” If in this example the nurseincreases the doe to 2 mg and the pattern shows an increase in severityan output such as “Pattern suggestive of moderated upper airwayinstability at dose of 2 mg/hr. of Versed-dose locked out”. To maintainVersed dose at the 2 mg, level in this patient the nurse or physicianwould have to override the lockout. Upon an override the processor thentracks the severity of the clusters and if the clusters reach aadditional severity threshold then an output such as “Severe upperairway instability—Versed locked out”

The anticipated range of time series for incorporation into thecylindrical relational matrix of streaming objects include; multiplepharmaceutical time series, exogenous action time series, monitoredsignal time series (which can include virtually any monitored parameteror its derivative), fluid balance, weight, and temperature time series,and time series or single timed data points of laboratory values(including chemistry, hematology, drug level monitoring, and procedurebased outputs (such as echocardiogram and pulmonary function testoutputs). Interpreted radiology results may also be incorporated as datapoints and once the digital signal for such testing can be reasonablysummarized to produce a time series, which reliably reflects a trend(such as the degree of pulmonary congestion), such outputs can also beinclude in the data matrix as time series for comparison with forexample the net fluid balance and weight time series. An additional timeseries can be the provided by nursing input, for example a time seriesof the pain index, or Ramsey Scale based level of sedation. This timeseries can be correlated with other monitored indices of sedation oranesthesia as is known in the art.

The cylindrical matrix of processed, analyzed, and objectified dataprovides an optimal new tool for the purpose of doing business todetermine, much more exactly, the dynamic factors, occurrences, andpatterns of relationships, which increase expense in any timed process.In the example of the hospital system discussed supra, the expense datais structured as a time series of objects with the data point valuerepresented by the total expense at each point. Expense values can belinked and or derived from certain procedures or laboratory tests, forexample the time series of the hemoglobin can be associated with acorresponding time series of the calculated expense for that test. Inthe preferred embodiment the plurality of time series of expense foreach monitored laboratory tests are combined to produce a global expensetime series. Individual time series time series for the expense of eachclass of exogenous actions (such as pharmaceutical, and procedural timeseries) is also provided and can then be combined to form one globalexpense time series. This is incorporated into the cylindrical datamatrix to provide discretionary comparison with dynamic expensevariables and dynamic patterns of relationships of other variables. Thisallows the hospital to determine the immediate expense related to theoccurrence of an episode of ventricular fibrillation. This expense canbe correlated with, for example, the timeliness of treatment, theapplication of different technologies, or the presence of a specificdynamic pattern of interaction of the signals. In other words theimmediate cost, and resources expended over, for example, the 24 hoursfollowing the episode of ventricular fibrillation, can be compared withthe true behavior and duration of the pathophysiologic componentsrelating the ventricular fibrillation episode.

In a further example consider a patient monitored with the presentinvention deriving a cylindrical data matrix comprised of streaming andoverlapping objects of airflow, chest wall impedance, EKG, oximetry, andglobal expense. The occurrence of the procedure for insertion of thecentral line represents an object (which need not have a variable value)along a segment of the cylinder. If the patent develops a pneumothoraxthe processor can early identify and warn of the development ofpathophysiologic divergence with respect to the airflow (and/or chestwall impedance) and the oxygen saturation (and/or pulse). In addition toearlier recognition, the expense related to this complication, thetimeliness of intervention, the magnitude of pathophysiologicperturbation due to the complication, and the resources expended tocorrect the complication can all be readily determined using theprocessor method and data structure of the present invention.

Many other additional new component cylinders may be added to thematrix. During the implementation of the present invention it isanticipated that many subtle relationships between the many componentswill become evident to those skilled in the art and these are includedwithin the scope of this invention. Those skilled in the art willrecognize that various changes and modifications can be made withoutdeparting from the invention. While the intention has been described inconnection with what is presently considered to be the most practicaland preferred embodiments, it is to be understood that the invention isnot to be limited to the disclosed embodiments, but on the contrary, is

In a further example consider a patient monitored with the presentinvention deriving a cylindrical data matrix comprised of streaming andoverlapping objects of airflow, chest wall impedance, EKG, oximetry, andglobal expense. The occurrence of the procedure for insertion of thecentral line represents an object (which need not have a variable value)along a segment of the cylinder. If the patent develops a pneumothoraxthe processor can early identify and warn of the development ofpathophysiologic divergence with respect to the airflow (and/or chestwall impedance) and the oxygen saturation (and/or pulse). In addition toearlier recognition, the expense related to this complication, thetimeliness of intervention, the magnitude of pathophysiologicperturbation due to the complication, and the resources expended tocorrect the complication can all be readily determined using theprocessor method and data structure of the present invention.

Many other additional new component cylinders may be added to thematrix. During the implementation of the present invention it isanticipated that many subtle relationships between the many componentswill become evident to those skilled in the art and these are includedwithin the scope of this invention. Those skilled in the art willrecognize that various changes and modifications can be made withoutdeparting from the invention. While the invention has been described inconnection with what is presently considered to be the most practicaland preferred embodiments, it is to be understood that the invention isnot to be limited to the disclosed embodiments, but on the contrary, isintended to cover various modifications and equivalent arrangementsincluded within the spirit and scope of the appended claims.

1) A microprocessor system for evaluation of a patient, the systemcomprising: a monitor having a plurality of sensors for positioningadjacent said patient and a processor programmed to: a) produce a firsttimed waveform based on a first physiologic parameter of a patient, b)produce a second timed waveform based on a second physiologic parameterwhich is generally subordinate to said first physiologic parameter, sothat said second parameter normally changes in response to changes insaid first parameter, c) identify pathophysiologic divergence of atleast one of said first and second physiologic parameters inrelationship to the other of said physiologic parameters, d) outputtingan indication of said divergence. 2) The system, as in claim 1, whereinthe processor is further programmed to: a) calculate an index of saiddivergence and, b) provide an indication based on said index. 3) Thesystem of claim 1, wherein said first parameter comprises at least oneof an indication and measure of the magnitude of timed ventilation of apatient. 4) The system of claim 1, wherein said second parametercomprises a measure of arterial oxygenation. 5) The system of claim 3,wherein said first parameter is at least one of the amplitude andfrequency of the variation in chest wall impedance. 6) The system ofclaim 3, wherein said first parameter is at least one of the amplitudeand frequency of the variation in nasal pressure. 7) The system of claim3, wherein said first parameter is at least one of the amplitude andfrequency of the variation of at least one of the tidal carbon dioxide.8) The system of claim 3, wherein the first parameter is measure of thetimed volume of at least one gaseous component of ventilation. 9) Amethod of monitoring a patient comprising: a) monitoring a patient toproduce a first timed waveform of a first physiologic parameter and asecond timed waveform of a second physiologic parameter, the secondphysiologic parameter being physiologically subordinate to said firstphysiologic parameter, b) identifying a pattern indicative of divergenceof at least one of said waveforms in relation to a physiologicallyexpected pattern of the other of said waveforms, c) outputting anindication of said divergence. 10) The system of claim 9, wherein saidfirst timed waveform is defined by a time interval of greater than about5-20 minutes. 11) The system of claim 9 wherein said first and secondtime series are physiologic time series derived from airflow and pulseoximetry. 12) The system of claim 9 wherein said processor comprises aprimary processor, said system further including a secondary processorand at least one of a diagnostic and treatment device, said primaryprocessor being connectable to said secondary processor, said secondaryprocessor being programmed to control at least one of said diagnosticand treatment device, said secondary processor being programmed torespond to the output of said primary processor. 13) The system of claim12 wherein said primary processor is programmed to adjust the saidprogram of said secondary processor. 14) The system of claim 12 whereinsaid treatment device is an airflow delivery system controlled by asecondary processor, said secondary processor being programmed torecognize hypopneas, said primary processor adjusting said program ofsaid secondary processor based on said identifying. 15) The system ofclaim 12 wherein said treatment device is an automatic defibrillator 16)The system of claim 12 wherein said secondary processor is mounted withat least one of said treatment and diagnostic device, said primaryprocessor being detachable from said connection with said secondaryprocessor. 17) The system of claim 12 wherein said primary processor ishospital patient monitor capable of monitoring and analyzing a pluralityof different patient related signals including electrocardiographicsignals. 18) The system of claim 12 wherein said primary processor is apolysomnography monitor capable of monitoring a plurality of differentsignals including encephalographic signals.